WO2020039639A1 - 画像処理装置、画像処理方法、プログラム - Google Patents

画像処理装置、画像処理方法、プログラム Download PDF

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Publication number
WO2020039639A1
WO2020039639A1 PCT/JP2019/013940 JP2019013940W WO2020039639A1 WO 2020039639 A1 WO2020039639 A1 WO 2020039639A1 JP 2019013940 W JP2019013940 W JP 2019013940W WO 2020039639 A1 WO2020039639 A1 WO 2020039639A1
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WIPO (PCT)
Prior art keywords
image
contrast agent
information
photoacoustic
image processing
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Ceased
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PCT/JP2019/013940
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English (en)
French (fr)
Japanese (ja)
Inventor
翔也 佐々木
長永　兼一
大樹 梶田
宣晶 今西
貞和 相磯
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Canon Inc
Keio University
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Canon Inc
Keio University
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Application filed by Canon Inc, Keio University filed Critical Canon Inc
Priority to CN201980054755.0A priority Critical patent/CN112584775B/zh
Priority to EP19850962.2A priority patent/EP3841982B1/en
Publication of WO2020039639A1 publication Critical patent/WO2020039639A1/ja
Priority to US17/178,403 priority patent/US12593985B2/en
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/14542—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue for measuring blood gases
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0075—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by spectroscopy, i.e. measuring spectra, e.g. Raman spectroscopy, infrared absorption spectroscopy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0093—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy
    • A61B5/0095—Detecting, measuring or recording by applying one single type of energy and measuring its conversion into another type of energy by applying light and detecting acoustic waves, i.e. photoacoustic measurements
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/74—Details of notification to user or communication with user or patient; User input means
    • A61B5/742—Details of notification to user or communication with user or patient; User input means using visual displays
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2576/00—Medical imaging apparatus involving image processing or analysis
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A61B5/0091—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for mammography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46—Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/461—Displaying means of special interest
    • A61B8/466—Displaying means of special interest adapted to display 3D data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/481—Diagnostic techniques involving the use of contrast agents, e.g. microbubbles introduced into the bloodstream
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/483—Diagnostic techniques involving the acquisition of a 3D volume of data

Definitions

  • the present invention relates to image processing on an image generated by photoacoustic imaging.
  • Patent Literature 1 discloses a photoacoustic image generation device that evaluates a contrast agent used for imaging lymph nodes, lymph vessels, and the like, and emits light having a wavelength that generates a photoacoustic wave when the contrast agent is absorbed. Is described.
  • an object of the present invention is to provide an image processing apparatus that generates a display image in which the structure of a contrast target can be easily grasped by photoacoustic imaging.
  • the image processing apparatus is based on a photoacoustic wave generated by irradiating a plurality of wavelengths different from each other to a subject into which a contrast agent has been introduced, to each of the plurality of wavelengths.
  • the image processing apparatus includes an area determining unit that determines an area corresponding to the contrast agent, and a display control unit that displays a spectral image so that the area corresponding to the contrast agent and an area other than the area can be identified.
  • an image processing apparatus that generates a display image in which the structure of a contrast target can be easily grasped by photoacoustic imaging.
  • FIG. 1 is a block diagram of a system according to an embodiment of the present invention.
  • FIG. 2 is a block diagram showing a specific example of an image processing apparatus according to an embodiment of the present invention and its peripheral configuration.
  • FIG. 3 is a detailed block diagram of the photoacoustic apparatus according to one embodiment of the present invention.
  • FIG. 4 is a schematic diagram of a probe according to one embodiment of the present invention.
  • FIG. 5 is a flowchart of an image processing method according to an embodiment of the present invention.
  • FIG. 6 is a graph showing an absorption coefficient spectrum when the concentration of ICG is changed.
  • FIGS. 7A to 7D are contour graphs of the calculated value of Expression (1) corresponding to the contrast agent when the combination of wavelengths is changed.
  • FIG. 8 is a line graph showing the calculated values of equation (1) corresponding to the contrast agent when the concentration of ICG is changed.
  • FIG. 9 is a graph showing a molar absorption coefficient spectrum of oxyhemoglobin and deoxyhemoglobin.
  • FIG. 10 is a diagram illustrating a GUI according to an embodiment of the present invention.
  • FIG. 11A and FIG. 11B are spectral images on the right forearm extension side when the density of ICG is changed.
  • 12A and 12B are spectral images on the left forearm extension side when the density of ICG is changed.
  • 13A and 13B are spectral images of the inside of the right lower leg and the inside of the left lower leg when the concentration of ICG is changed.
  • the photoacoustic image obtained by the system according to the present invention reflects the absorption amount and absorption rate of light energy.
  • the photoacoustic image is an image representing a spatial distribution of at least one object information such as a generated sound pressure (initial sound pressure) of a photoacoustic wave, a light absorption energy density, and a light absorption coefficient.
  • the photoacoustic image may be an image representing a two-dimensional spatial distribution or an image (volume data) representing a three-dimensional spatial distribution.
  • the system according to the present embodiment generates a photoacoustic image by photographing a subject into which a contrast agent has been introduced. In order to grasp the three-dimensional structure of the contrast target, the photoacoustic image may be an image representing a two-dimensional spatial distribution or a three-dimensional spatial distribution in a depth direction from the subject surface.
  • the system according to the present invention can generate a spectral image of the subject using a plurality of photoacoustic images corresponding to a plurality of wavelengths.
  • the spectral image of the present invention is based on a photoacoustic wave generated by irradiating a subject with light of a plurality of different wavelengths, and is an image generated using a photoacoustic signal corresponding to each of the plurality of wavelengths. is there.
  • the spectral image may be an image generated using the photoacoustic signals corresponding to each of the plurality of wavelengths and indicating the concentration of the specific substance in the subject.
  • the image value of the contrast agent in the spectral image and the image value of the specific substance in the spectral image are different. Therefore, the region of the contrast agent and the region of the specific substance can be distinguished according to the image value of the spectral image.
  • a substance constituting the subject such as hemoglobin, glucose, collagen, melanin, fat and water, may be mentioned. Also in this case, it is necessary to select a contrast agent having a light absorption spectrum different from the light absorption coefficient spectrum of the specific substance. Further, the spectral image may be calculated by a different calculation method according to the type of the specific substance.
  • an image calculated using the oxygen saturation calculation formula (1) will be described as a spectral image.
  • the present inventors have calculated the optical saturation of blood hemoglobin based on the photoacoustic signal corresponding to each of the plurality of wavelengths (or an index having a correlation with the oxygen saturation).
  • I (r) of a photoacoustic signal obtained with a contrast agent whose wavelength dependence of the absorption coefficient is different from that of oxyhemoglobin and deoxyhemoglobin is substituted, the numerical range in which the oxygen saturation of hemoglobin can be taken From the calculated value Is (r).
  • Is (r) is a measurement value based on a photoacoustic wave generated by light irradiation of the first wavelength ⁇ 1
  • I ⁇ 2 (r) is generated by light irradiation of the second wavelength ⁇ 2 This is a measurement value based on a photoacoustic wave.
  • ⁇ Hb ⁇ 1 is a molar absorption coefficient of deoxyhemoglobin corresponding to the first wavelength ⁇ 1 [mm ⁇ 1 mol ⁇ 1 ]
  • ⁇ Hb ⁇ 2 is a molar absorption coefficient of deoxy hemoglobin corresponding to the second wavelength ⁇ 2 [ mm -1 mol -1 ].
  • ⁇ HbO ⁇ 1 is the molar absorption coefficient of oxyhemoglobin corresponding to the first wavelength ⁇ 1 [mm ⁇ 1 mol ⁇ 1 ]
  • ⁇ HbO ⁇ 2 is the molar absorption coefficient of oxyhemoglobin corresponding to the second wavelength ⁇ 2 [ mm -1 mol -1 ].
  • r is a position.
  • the absorption coefficients ⁇ a ⁇ 1 (r) and ⁇ a ⁇ 2 (r) may be used, or the initial sound pressure P 0 ⁇ 1 (r) and P 0 ⁇ 2 (r) may be used.
  • the numerical value of the molar absorption coefficient of hemoglobin may be used as it is in Expression (1).
  • the spectral image Is (r) obtained in this manner is in a state where both the hemoglobin existing region (blood vessel) and the contrast agent existing region (for example, lymphatic vessel) inside the subject are separable from each other (can be distinguished). The image is rendered.
  • the image value of the spectral image is calculated using Expression (1) for calculating the oxygen saturation.
  • Expression (1) for calculating the oxygen saturation.
  • the expression A calculation method other than (1) may be used.
  • the index and the method for calculating the index known ones can be used, and a detailed description thereof will be omitted here.
  • the system according to the present invention was based on the photoacoustic wave generated by the first light irradiation of the photoacoustic image and the second wavelength lambda 2, based on the photoacoustic wave generated by light irradiation of the first wavelength lambda 1
  • An image indicating the ratio of the two photoacoustic images may be used as the spectral image. That is, the ratio of the second photoacoustic image based on the photoacoustic wave generated by light irradiation of the first photoacoustic image and the second wavelength lambda 2, based on the photoacoustic wave generated by light irradiation of the first wavelength lambda 1
  • the image based on this may be a spectral image.
  • an image generated according to the modified expression of Expression (1) can also be expressed by the ratio between the first photoacoustic image and the second photoacoustic image.
  • Image (spectral image) can also be expressed by the ratio between the first photoacoustic image and the
  • the spectral image may be an image representing a two-dimensional spatial distribution in the depth direction from the surface of the subject or an image representing a three-dimensional spatial distribution.
  • FIG. 1 is a block diagram illustrating a configuration of a system according to the present embodiment.
  • the system according to the present embodiment includes a photoacoustic device 1100, a storage device 1200, an image processing device 1300, a display device 1400, and an input device 1500. Transmission and reception of data between the devices may be performed by wire or wirelessly.
  • the photoacoustic apparatus 1100 generates a photoacoustic image by capturing an image of a subject into which a contrast agent is introduced, and outputs the photoacoustic image to the storage device 1200.
  • the photoacoustic device 1100 is a device that generates information of characteristic values corresponding to each of a plurality of positions in a subject using a reception signal obtained by receiving a photoacoustic wave generated by light irradiation. That is, the photoacoustic apparatus 1100 is an apparatus that generates a spatial distribution of characteristic value information derived from a photoacoustic wave as medical image data (photoacoustic image).
  • the storage device 1200 may be a storage medium such as a ROM (Read Only Memory), a magnetic disk, or a flash memory. Further, the storage device 1200 may be a storage server via a network such as a PACS (Picture Archiving and Communication System).
  • a storage medium such as a ROM (Read Only Memory), a magnetic disk, or a flash memory. Further, the storage device 1200 may be a storage server via a network such as a PACS (Picture Archiving and Communication System).
  • PACS Picture Archiving and Communication System
  • the image processing device 1300 is a device that processes information such as a photoacoustic image and incidental information of the photoacoustic image stored in the storage device 1200.
  • a unit having an arithmetic function of the image processing apparatus 1300 can be configured by an arithmetic circuit such as a CPU, a processor such as a GPU (Graphics Processing Unit), or an FPGA (Field Programmable Gate Array) chip. These units may be configured not only from a single processor or arithmetic circuit, but also from a plurality of processors or arithmetic circuits.
  • a unit having a storage function of the image processing apparatus 1300 can be configured by a non-temporary storage medium such as a ROM (Read Only Memory), a magnetic disk, or a flash memory.
  • the unit having the storage function may be a volatile medium such as a RAM (Random Access Memory).
  • the storage medium on which the program is stored is a non-temporary storage medium.
  • the unit having the storage function is not limited to a single storage medium, and may be configured from a plurality of storage media.
  • a unit having a control function of the image processing apparatus 1300 is configured by an arithmetic element such as a CPU.
  • a unit having a control function controls the operation of each component of the system.
  • the unit having the control function may control each component of the system in response to an instruction signal from various operations such as the start of measurement from the input unit. Further, the unit having the control function may read out the program code stored in the computer 150 and control the operation of each component of the system.
  • the display device 1400 is a display such as a liquid crystal display or an organic EL (Electro Luminescence).
  • the display device 1400 may display an image or a GUI for operating the device.
  • an operation console that can be operated by a user and includes a mouse, a keyboard, and the like can be employed.
  • the display device 1400 may be configured with a touch panel, and the display device 1400 may be used as the input device 1500.
  • FIG. 2 shows a specific configuration example of the image processing apparatus 1300 according to the present embodiment.
  • the image processing apparatus 1300 according to the present embodiment includes a CPU 1310, a GPU 1320, a RAM 1330, a ROM 1340, and an external storage device 1350.
  • a liquid crystal display 1410 as a display device 1400, a mouse 1510 as an input device 1500, and a keyboard 1520 are connected to the image processing device 1300.
  • the image processing apparatus 1300 is connected to an image server 1210 as a storage device 1200 such as a PACS (Picture Archiving and Communication System).
  • the image data can be stored on the image server 1210 or the image data on the image server 1210 can be displayed on the liquid crystal display 1410.
  • FIG. 3 is a schematic block diagram of devices included in the system according to the present embodiment.
  • the photoacoustic apparatus 1100 includes a drive unit 130, a signal collection unit 140, a computer 150, a probe 180, and an introduction unit 190.
  • the probe 180 has a light irradiation unit 110 and a reception unit 120.
  • FIG. 4 is a schematic diagram of the probe 180 according to the present embodiment.
  • the measurement target is the subject 100 into which the contrast agent has been introduced by the introduction unit 190.
  • the drive unit 130 drives the light irradiation unit 110 and the reception unit 120 to perform mechanical scanning.
  • the light irradiation unit 110 irradiates the subject 100 with light, and an acoustic wave is generated in the subject 100.
  • An acoustic wave generated by the photoacoustic effect due to light is also called a photoacoustic wave.
  • the receiving unit 120 outputs an electric signal (photoacoustic signal) as an analog signal by receiving the photoacoustic wave.
  • the signal collecting unit 140 converts the analog signal output from the receiving unit 120 into a digital signal, and outputs the digital signal to the computer 150.
  • the computer 150 stores the digital signal output from the signal collection unit 140 as signal data derived from a photoacoustic wave.
  • the computer 150 generates a photoacoustic image by performing signal processing on the stored digital signal.
  • the computer 150 outputs the photoacoustic image to the display unit 160 after performing image processing on the obtained photoacoustic image.
  • the display unit 160 displays an image based on the photoacoustic image.
  • the display image is stored in a memory in the computer 150 or a storage device 1200 such as a data management system connected to the modality via a network based on a storage instruction from the user or the computer 150.
  • the computer 150 also performs drive control of components included in the photoacoustic device.
  • the display unit 160 may display a GUI or the like in addition to the image generated by the computer 150.
  • the input unit 170 is configured to allow a user to input information. The user can use the input unit 170 to perform operations such as start and end of measurement, and an instruction to save a created image.
  • details of each configuration of the photoacoustic apparatus 1100 according to the present embodiment will be described.
  • the light irradiation unit 110 includes a light source 111 that emits light, and an optical system 112 that guides light emitted from the light source 111 to the subject 100.
  • the light includes pulse light such as a so-called rectangular wave and a triangular wave.
  • the pulse width of the light emitted from the light source 111 is preferably 100 ns or less in consideration of the thermal confinement condition and the stress confinement condition. Further, the wavelength of the light may be in the range of about 400 nm to 1600 nm. When imaging a blood vessel with high resolution, a wavelength (400 nm or more and 700 nm or less) at which absorption in the blood vessel is large may be used. When imaging a deep part of a living body, light having a wavelength (700 nm or more and 1100 nm or less) that typically absorbs little in a background tissue (water or fat) of the living body may be used.
  • a laser or a light emitting diode can be used.
  • a light source whose wavelength can be changed may be used.
  • a plurality of light sources are used, they are collectively expressed as a light source.
  • Various lasers such as a solid-state laser, a gas laser, a dye laser, and a semiconductor laser can be used as the laser.
  • a pulsed laser such as an Nd: YAG laser or an alexandrite laser may be used as a light source.
  • a Ti: sa laser using Nd: YAG laser light as excitation light or an OPO (Optical Parametric Oscillators) laser may be used as a light source.
  • a flash lamp or a light emitting diode may be used as the light source 111.
  • a microwave source may be used as the light source 111.
  • Optical elements such as lenses, mirrors, and optical fibers can be used for the optical system 112.
  • the light emitting unit of the optical system may be configured with a diffusion plate or the like that diffuses light in order to irradiate the pulsed light with a wider beam diameter.
  • the light emitting portion of the optical system 112 may be configured by a lens or the like, and the beam may be focused and irradiated.
  • the light irradiating unit 110 may directly irradiate the subject 100 with light from the light source 111 without including the optical system 112.
  • the receiving unit 120 includes a transducer 121 that outputs an electric signal by receiving an acoustic wave, and a support 122 that supports the transducer 121. Further, the transducer 121 may be a transmitting unit that transmits an acoustic wave.
  • the transducer as the receiving means and the transducer as the transmitting means may be a single (common) transducer or may have different configurations.
  • a piezoelectric ceramic material represented by PZT lead zirconate titanate
  • a polymer piezoelectric film material represented by PVDF polyvinylidene fluoride
  • an element other than the piezoelectric element may be used.
  • a transducer using a capacitance type micro-machined Ultrasonic Transducers (CMUT) can be used. Note that any transducer may be employed as long as an electrical signal can be output by receiving an acoustic wave. The signal obtained by the transducer is a time-resolved signal.
  • the amplitude of the signal obtained by the transducer indicates a value based on the sound pressure received by the transducer at each time (for example, a value proportional to the sound pressure).
  • the frequency component constituting the photoacoustic wave is typically 100 KHz to 100 MHz, and a transducer that can detect these frequencies may be employed as the transducer 121.
  • the support 122 may be made of a metal material having high mechanical strength. In order to cause a large amount of irradiation light to enter the subject, the surface of the support 122 on the subject 100 side may be subjected to mirror finishing or light scattering.
  • the support 122 has a hemispherical shell shape, and is configured to be able to support the plurality of transducers 121 on the hemispherical shell. In this case, the directional axes of the transducers 121 disposed on the support body 122 gather near the center of curvature of the hemisphere. Then, when an image is formed using the signals output from the plurality of transducers 121, the image quality near the center of curvature becomes high.
  • the support 122 may have any configuration as long as it can support the transducer 121.
  • the support 122 may arrange a plurality of transducers in a plane or a curved surface such as a 1D array, a 1.5D array, a 1.75D array, and a 2D array.
  • the plurality of transducers 121 correspond to a plurality of receiving units.
  • the support 122 may function as a container for storing the acoustic matching material. That is, the support 122 may be a container for disposing the acoustic matching material between the transducer 121 and the subject 100.
  • the receiving unit 120 may include an amplifier that amplifies a time-series analog signal output from the transducer 121. Further, the receiving unit 120 may include an A / D converter that converts a time-series analog signal output from the transducer 121 into a time-series digital signal. That is, the receiving unit 120 may include a signal collecting unit 140 described later.
  • the space between the receiving unit 120 and the subject 100 is filled with a medium through which a photoacoustic wave can propagate.
  • a medium a material that can transmit an acoustic wave, has matching acoustic characteristics at the interface with the subject 100 and the transducer 121, and has the highest possible transmittance of the photoacoustic wave is used.
  • water, an ultrasonic gel, or the like can be used as the medium.
  • FIG. 4 shows a side view of the probe 180.
  • the probe 180 according to the present embodiment has a receiving unit 120 in which a plurality of transducers 121 are three-dimensionally arranged on a hemispherical support body 122 having an opening.
  • a light emitting portion of the optical system 112 is disposed at the bottom of the support 122.
  • the shape of the subject 100 is held by contacting the holding unit 200.
  • the space between the receiving unit 120 and the holding unit 200 is filled with a medium through which a photoacoustic wave can propagate.
  • a medium a material that can transmit a photoacoustic wave, matches acoustic characteristics at the interface with the subject 100 and the transducer 121, and has a transmittance of the photoacoustic wave as high as possible is used.
  • water, an ultrasonic gel, or the like can be used as the medium.
  • the holding unit 200 as a holding unit is used to hold the shape of the subject 100 during measurement. By holding the subject 100 by the holding unit 200, the movement of the subject 100 can be suppressed and the position of the subject 100 can be kept in the holding unit 200.
  • a resin material such as polycarbonate, polyethylene, or polyethylene terephthalate can be used as the material of the holding section 200.
  • the holding unit 200 is attached to the attachment unit 201.
  • the attachment unit 201 may be configured so that a plurality of types of holding units 200 can be exchanged according to the size of the subject.
  • the mounting portion 201 may be configured to be exchangeable with a different holding portion such as a radius of curvature or a center of curvature.
  • the driving unit 130 is a unit that changes the relative position between the subject 100 and the receiving unit 120.
  • the driving unit 130 includes a motor such as a stepping motor that generates a driving force, a driving mechanism that transmits the driving force, and a position sensor that detects position information of the receiving unit 120.
  • a motor such as a stepping motor that generates a driving force
  • a driving mechanism that transmits the driving force
  • a position sensor that detects position information of the receiving unit 120.
  • As the driving mechanism a lead screw mechanism, a link mechanism, a gear mechanism, a hydraulic mechanism, or the like can be used.
  • As the position sensor a potentiometer using an encoder, a variable resistor, a linear scale, a magnetic sensor, an infrared sensor, an ultrasonic sensor, or the like can be used.
  • the driving unit 130 is not limited to changing the relative position between the subject 100 and the receiving unit 120 in the XY directions (two-dimensional), and may change the relative position to one-dimensional or three-dimensional.
  • the drive unit 130 may fix the receiving unit 120 and move the subject 100 as long as the relative position between the subject 100 and the receiving unit 120 can be changed.
  • the drive unit 130 may move the relative position continuously, or may move the relative position by step and repeat.
  • the drive unit 130 may be an electric stage that moves along a programmed trajectory, or may be a manual stage.
  • the driving unit 130 scans by simultaneously driving the light irradiation unit 110 and the reception unit 120.
  • the drive unit 130 drives only the light irradiation unit 110 or drives only the reception unit 120. You may.
  • the photoacoustic device 1100 may not include the driving unit 130.
  • the signal collection unit 140 includes an amplifier that amplifies an electric signal that is an analog signal output from the transducer 121, and an A / D converter that converts an analog signal output from the amplifier into a digital signal.
  • the digital signal output from the signal collection unit 140 is stored in the computer 150.
  • the signal collection unit 140 is also called a Data Acquisition System (DAS).
  • DAS Data Acquisition System
  • the electric signal is a concept including both an analog signal and a digital signal.
  • a light detection sensor such as a photodiode may detect light emission from the light irradiation unit 110, and the signal collection unit 140 may start the above process in synchronization with the detection result in response to a trigger.
  • the computer 150 as the information processing device is configured by the same hardware as the image processing device 1300. That is, the unit having the arithmetic function of the computer 150 can be configured by an arithmetic circuit such as a processor such as a CPU or a GPU (Graphics Processing Unit) or an FPGA (Field Programmable Gate Array) chip. These units may be configured not only from a single processor or arithmetic circuit, but also from a plurality of processors or arithmetic circuits.
  • the unit that performs the storage function of the computer 150 may be a volatile medium such as a RAM (Random Access Memory).
  • the storage medium on which the program is stored is a non-temporary storage medium. It should be noted that the unit having the storage function of the computer 150 may not only be constituted by one storage medium, but also constituted by a plurality of storage media.
  • the unit that performs the control function of the computer 150 is composed of an arithmetic element such as a CPU.
  • a unit having a control function of the computer 150 controls the operation of each component of the photoacoustic apparatus.
  • a unit having a control function of the computer 150 may control each component of the photoacoustic apparatus by receiving an instruction signal from the input unit 170 through various operations such as a start of measurement. Further, the unit having the control function of the computer 150 reads out the program code stored in the unit having the storage function, and controls the operation of each component of the photoacoustic apparatus. That is, the computer 150 can function as a control device of the system according to the present embodiment.
  • the computer 150 and the image processing device 1300 may be configured by the same hardware.
  • One piece of hardware may perform the functions of both the computer 150 and the image processing device 1300. That is, the computer 150 may perform the function of the image processing apparatus 1300. Further, the image processing device 1300 may have the function of the computer 150 as the information processing device.
  • the display unit 160 is a display such as a liquid crystal display and an organic EL (Electro Luminescence).
  • the display unit 160 may display an image or a GUI for operating the apparatus. Note that the display unit 160 and the display device 1400 may be the same display. That is, one display may have the functions of both the display unit 160 and the display device 1400.
  • Input unit 170 As the input unit 170, an operation console that can be operated by a user and includes a mouse and a keyboard can be employed. Further, the display unit 160 may be configured by a touch panel, and the display unit 160 may be used as the input unit 170. Note that the input unit 170 and the input device 1500 may be the same device. That is, one device may perform both functions of the input unit 170 and the input device 1500.
  • the introduction unit 190 is configured to be able to introduce a contrast agent from outside the subject 100 into the inside of the subject 100.
  • the introducer 190 can include a container for the contrast agent and a needle for piercing the subject.
  • the present invention is not limited to this, and various types can be applied to the introduction unit 190 as long as the contrast agent can be introduced into the subject 100.
  • the introduction unit 190 may be, for example, a known injection system, an injector, or the like.
  • the contrast agent may be introduced into the subject 100 by controlling the operation of the introduction unit 190 by the computer 150 as a control device. Further, the contrast agent may be introduced into the subject 100 by operating the introduction unit 190 by the user.
  • the subject 100 does not constitute a system, but will be described below.
  • the system according to the present embodiment can be used for the purpose of diagnosing malignant tumors and vascular diseases of humans and animals, monitoring the progress of chemotherapy and the like. Therefore, the subject 100 is assumed to be a body to be diagnosed, specifically, a living body, specifically, a breast or each organ of a human body or an animal, a vascular network, a head, a neck, an abdomen, a limb including a finger or a toe. You.
  • the human body is a measurement target
  • oxyhemoglobin or deoxyhemoglobin a blood vessel containing many of them, a new blood vessel formed near a tumor, or the like may be the target of the light absorber.
  • plaque of the carotid artery wall or the like may be a target of the light absorber.
  • melanin, collagen, lipids, and the like contained in the skin and the like may be targeted for the light absorber.
  • the contrast agent introduced into the subject 100 can be a light absorber.
  • a dye such as indocyanine green (ICG) or methylene blue (MB), a fine gold particle, a mixture thereof, or a substance which is integrated or chemically modified and externally introduced is used. May be. Further, a phantom imitating a living body may be used as the subject 100.
  • Each configuration of the photoacoustic device may be configured as a separate device, or may be configured as one integrated device. Further, at least a part of the configuration of the photoacoustic apparatus may be configured as one integrated apparatus.
  • Each device constituting the system according to the present embodiment may be constituted by separate hardware, or all devices may be constituted by one piece of hardware. The function of the system according to the present embodiment may be configured by any hardware.
  • the flowchart shown in FIG. 5 includes a step indicating the operation of the system according to the present embodiment and a step indicating the operation of a user such as a doctor.
  • the computer 150 of the photoacoustic apparatus 1100 obtains examination order information transmitted from an in-hospital information system such as a Hospital Information System (HIS) or a Radiology Information System (RIS).
  • the examination order information includes information such as the type of the modality used for the examination and the contrast agent used for the examination.
  • the computer 150 as a contrast agent information acquisition unit acquires information on a contrast agent.
  • the user may use the input unit 170 to specify the type of the contrast agent to be used for the examination and the concentration of the contrast agent.
  • the computer 150 can acquire information on the contrast agent via the input unit 170.
  • the examination order information acquired in S100 includes information on the contrast agent
  • the computer 150 may acquire the information by reading out the information on the contrast agent from the examination order information.
  • the computer 150 may acquire information on the contrast agent based on at least one of a user instruction and examination order information.
  • the information on the contrast agent indicating the condition of the contrast agent includes the type of the contrast agent, the concentration of the contrast agent, and the like.
  • FIG. 10 shows an example of a GUI displayed on the display unit 160.
  • examination order information such as a patient ID, an examination ID, and an imaging date and time is displayed.
  • the item 2500 may have a display function of displaying inspection order information acquired from an external device such as a HIS or RIS, or an input function of allowing a user to input inspection order information using the input unit 170.
  • the GUI item 2600 displays information on the contrast agent such as the type of the contrast agent and the concentration of the contrast agent.
  • the item 2600 may have a display function of displaying information on a contrast agent acquired from an external device such as an HIS or RIS, or an input function that allows a user to input information on a contrast agent using the input unit 170. Good.
  • information on the contrast agent such as the type and concentration of the contrast agent may be input from a plurality of options by a method such as pull-down. Note that the GUI shown in FIG. 10 may be displayed on the display device 1400.
  • the information on the contrast agent set by default may be acquired from the information on the plurality of contrast agents.
  • ICG is set as the type of the contrast agent
  • 1.0 mg / mL is set as the concentration of the contrast agent by default.
  • the type and density of the contrast agent set by default are displayed in the item 2600 of the GUI, but the information on the contrast agent may not be set by default. In this case, the information about the contrast agent may not be displayed on the GUI item 2600 on the initial screen.
  • the introduction unit 190 introduces a contrast agent into the subject.
  • the user operates the input unit 170 to send a signal indicating that the contrast agent has been introduced from the input unit 170 to the control device. It may be transmitted to the computer 150. Further, the introduction unit 190 may transmit a signal indicating that the contrast agent has been introduced into the subject 100 to the computer 150.
  • the contrast agent may be administered to the subject without using the introduction unit 190.
  • the contrast medium may be administered by aspirating the sprayed contrast medium onto a living body as a subject.
  • S400 which will be described later, may be executed after a period of time until the contrast agent reaches the contrast target in the subject 100.
  • the computer 150 as the wavelength determining means determines the wavelength of the irradiation light based on the information on the contrast agent acquired in S200. In this embodiment, in order to generate a spectral image, the computer 150 determines a plurality of wavelengths based on information about a contrast agent.
  • a combination of wavelengths for facilitating identification of a region corresponding to a contrast agent in a spectral image will be described.
  • an image according to Expression (1) is generated as a spectral image in S800 described below.
  • equation (1) for a blood vessel region in the spectral image, an image value corresponding to the actual oxygen saturation is calculated.
  • the image value greatly changes depending on the wavelength used.
  • the image value greatly varies depending on the absorption coefficient spectrum of the contrast agent.
  • the image value of the contrast agent region in the spectral image may be a value that cannot be distinguished from the image value of the blood vessel region.
  • the image value of the region of the contrast agent in the spectral image be a value that can be distinguished from the image value of the region of the blood vessel.
  • the present inventors have conceived of controlling the image value of the region of the contrast agent in the spectral image by adaptively changing the wavelength of the irradiation light according to the condition of the contrast agent used for the inspection. . That is, the inventor has devised that the information processing apparatus determines the wavelength of the irradiation light that can identify the region of the contrast agent and the region of the blood vessel in the spectral image based on the information on the contrast agent.
  • the wavelength of the irradiation light is determined by utilizing that the oxygen saturation of the artery and vein falls within approximately 60% to 100% in percent display. May be. That is, the computer 150 serving as the information processing apparatus determines that the value of the expression (1) corresponding to the contrast agent in the spectral image is smaller than 60% or larger than 100% based on the information regarding the contrast agent. Two wavelengths may be determined. Also, the computer 150 determines two wavelengths based on the information on the contrast agent such that the signs of the image values of the region corresponding to the contrast agent in the spectral image and the image values of the other regions are reversed. Is also good.
  • FIG. 6 is a spectrum diagram showing a change in the absorption coefficient spectrum when the concentration of ICG as a contrast agent is changed.
  • FIG. 6 shows spectrum diagrams in the case where the concentration of ICG is 5.04 ⁇ g / mL, 50.4 ⁇ g / mL, 0.5 mg / mL, and 1.0 mg / mL in order from the bottom. As shown in FIG. 6, it is understood that the light absorption degree increases as the concentration of the contrast agent increases.
  • the ratio of the absorption coefficients corresponding to the two wavelengths changes according to the concentration of the contrast agent
  • the image value corresponding to the contrast agent in the spectral image changes according to the concentration of the contrast agent. Is done.
  • the ratio of the absorption coefficients corresponding to the two wavelengths also changes when the type of the contrast agent changes. Therefore, it is understood that the image value corresponding to the contrast agent in the spectral image changes even according to the type of the contrast agent.
  • FIGS. 11A to 13B show spectral images obtained by photographing when ICG is introduced while changing the density.
  • 0.1 mL of ICG was introduced subcutaneously or intradermally on the hand or foot at each location.
  • the ICG introduced subcutaneously or intradermally is selectively taken up by the lymphatic vessels, so that the lumen of the lymphatic vessels is imaged.
  • the images were taken within 5 to 60 minutes after the introduction of ICG.
  • Each of the spectral images is a spectral image generated from a photoacoustic image obtained by irradiating a living body with light having a wavelength of 797 nm and light having a wavelength of 835 nm.
  • FIG. 11A shows a spectral image on the right forearm extension side when ICG is not introduced.
  • FIG. 11B shows a spectral image on the right forearm extension side when ICG having a concentration of 2.5 mg / mL was introduced.
  • the lymphatic vessels are depicted in the area indicated by the broken line and the arrow in FIG. 11B.
  • FIG. 12A shows a spectral image of the left forearm extension when ICG having a concentration of 1.0 mg / mL is introduced.
  • FIG. 12B shows a spectral image of the left forearm extension when ICG having a concentration of 5.0 mg / mL was introduced. Lymph vessels are depicted in the area indicated by the broken line and the arrow in FIG.
  • FIG. 13A shows a spectral image of the inside of the right lower leg when ICG having a concentration of 0.5 mg / mL is introduced.
  • FIG. 13B shows a spectral image of the inside of the left lower leg when ICG having a concentration of 5.0 mg / mL is introduced. Lymph vessels are depicted in the area indicated by the broken line and the arrow in FIG. 13B.
  • the visibility of the lymphatic vessels in the spectral images is improved when the concentration of ICG is increased.
  • the lymph vessels can be favorably visualized when the concentration of ICG is 2.5 mg / mL or more. That is, when the concentration of ICG is 2.5 mg / mL or more, the lymph vessels on the line can be clearly recognized. Therefore, when ICG is used as a contrast agent, the concentration may be 2.5 mg / mL or more. In consideration of the dilution of ICG in a living body, the concentration of ICG may be higher than 5.0 mg / mL.
  • the concentration of ICG to be introduced into a living body is preferably 2.5 mg / mL or more and 10.0 mg / mL or less, and more preferably 5.0 mg / mL or more and 10.0 mg / mL or less.
  • the computer 150 is configured to selectively receive an instruction from the user indicating the concentration of ICG in the above numerical range when ICG is input as the type of the contrast agent in the item 2600 of the GUI shown in FIG. May be. That is, in this case, the computer 150 may be configured not to receive an instruction from the user indicating the ICG concentration outside the above numerical range. Therefore, when acquiring information indicating that the type of the contrast agent is ICG, the computer 150 issues an instruction from a user indicating a concentration of ICG smaller than 2.5 mg / mL or larger than 10.0 mg / mL. May not be accepted.
  • the computer 150 when acquiring information indicating that the type of the contrast agent is ICG, the computer 150 receives an instruction from the user indicating a concentration of ICG smaller than 5.0 mg / mL or larger than 10.0 mg / mL. You may be comprised so that it may not accept.
  • the computer 150 may configure the GUI so that the user cannot specify the ICG concentration outside the above numerical range on the GUI. That is, the computer 150 may display the GUI so that the user cannot specify the ICG concentration outside the numerical range on the GUI. For example, the computer 150 may display a pull-down on the GUI that can selectively indicate the concentration of ICG in the above numerical range. The computer 150 may display the density of the ICG outside the numerical range in the pull-down by graying out the density, and may configure the GUI so that the grayed-out density cannot be selected.
  • the computer 150 may notify an alert when a user specifies an ICG concentration outside the above numerical range on the GUI.
  • the notification method any method such as displaying an alert on the display unit 160 and lighting a sound or a lamp can be adopted.
  • the computer 150 may cause the display unit 160 to display the above numerical range as the concentration of ICG to be introduced into the subject.
  • the concentration of the contrast agent to be introduced into the subject is not limited to the numerical range shown here, and a suitable concentration according to the purpose can be adopted. Further, here, an example in which the type of the contrast agent is ICG has been described, but the above configuration can be similarly applied to other contrast agents. By configuring the GUI in this manner, it is possible to support the user to introduce an appropriate contrast agent concentration into the subject according to the type of the contrast agent to be introduced into the subject.
  • 7A to 7D show simulation results of image values (oxygen saturation values) corresponding to the contrast agent in the spectral image in each of the two wavelength combinations.
  • 7A to 7D represent the first wavelength and the second wavelength, respectively.
  • 7A to 7D show contour lines of image values corresponding to the contrast agent in the spectral images.
  • 7A to 7D show image values corresponding to a contrast agent in a spectral image when the concentration of ICG is 5.04 ⁇ g / mL, 50.4 ⁇ g / mL, 0.5 mg / mL, and 1.0 mg / mL, respectively. Show.
  • the image value corresponding to the contrast agent in the spectral image may be 60% to 100% depending on the combination of the selected wavelengths. As described above, if such a combination of wavelengths is selected, it becomes difficult to distinguish a blood vessel region and a contrast agent region in a spectral image. Therefore, in the wavelength combinations shown in FIGS. 7A to 7D, it is preferable to select a wavelength combination such that the image value corresponding to the contrast agent in the spectral image is smaller than 60% or larger than 100%. . Further, it is preferable to select a combination of wavelengths such that the image value corresponding to the contrast agent in the spectral image has a negative value in the combination of wavelengths shown in FIGS. 7A to 7D.
  • FIG. 8 shows the relationship between the concentration of ICG and the image value (the value of equation (1)) corresponding to the contrast agent in the spectral image when 797 nm is selected as the first wavelength and 835 nm is selected as the second wavelength.
  • FIG. 8 shows the relationship between the concentration of ICG and the image value (the value of equation (1)) corresponding to the contrast agent in the spectral image when 797 nm is selected as the first wavelength and 835 nm is selected as the second wavelength.
  • the contrast in the spectral image is increased regardless of the concentration of 5.04 ⁇ g / mL to 1.0 mg / mL.
  • the image value corresponding to the agent is a negative value. Therefore, according to the spectral image generated by such a combination of wavelengths, since the oxygen saturation value of the blood vessel does not take a negative value in principle, the blood vessel region and the contrast agent region are clearly distinguished. be able to.
  • the wavelength is determined based on the information on the contrast agent.
  • the absorption coefficient of hemoglobin may be considered in determining the wavelength.
  • FIG. 9 shows the spectrum of the molar absorption coefficient of oxyhemoglobin (dashed line) and the molar absorption coefficient of deoxyhemoglobin (solid line).
  • the magnitude relationship between the molar absorption coefficient of oxyhemoglobin and the molar absorption coefficient of deoxyhemoglobin is reversed at the boundary of 797 nm. That is, it can be said that it is easy to grasp the vein at a wavelength shorter than 797 nm, and it is easy to grasp the artery at a wavelength longer than 797 nm.
  • lymphatic venule anastomosis for creating a bypass between lymphatic vessels and veins is used.
  • photoacoustic imaging to image both the veins and the lymph vessels in which the contrast agent has accumulated.
  • at least one of the plurality of wavelengths is set to a wavelength at which the molar absorption coefficient of deoxyhemoglobin is larger than the molar absorption coefficient of oxyhemoglobin.
  • the vein is imaged by setting the wavelength at which the molar absorption coefficient of deoxyhemoglobin is larger than the molar absorption coefficient of oxyhemoglobin at any of the two wavelengths. This is advantageous. By selecting these wavelengths, in the preoperative examination of the lymphatic venule anastomosis, it is possible to accurately image both the lymphatic vessels and the veins into which the contrast agent has been introduced.
  • any of the plurality of wavelengths is a wavelength at which the absorption coefficient of the contrast agent is larger than that of blood, the oxygen saturation accuracy of the blood decreases due to artifacts derived from the contrast agent. Therefore, in order to reduce artifacts derived from the contrast agent, at least one of the plurality of wavelengths may be a wavelength at which the absorption coefficient of the contrast agent is smaller than the absorption coefficient of blood.
  • the light irradiation unit 110 sets the wavelength determined in S400 to the light source 111.
  • the light source 111 emits light having the wavelength determined in S400.
  • Light generated from the light source 111 is applied to the subject 100 as pulse light via the optical system 112. Then, the pulse light is absorbed inside the subject 100, and a photoacoustic wave is generated by the photoacoustic effect. At this time, the introduced contrast agent also absorbs the pulse light and generates a photoacoustic wave.
  • the light irradiation unit 110 may transmit a synchronization signal to the signal collection unit 140 together with the transmission of the pulse light.
  • the light irradiating unit 110 similarly irradiates each of a plurality of wavelengths with light.
  • the user may specify the control parameters such as the irradiation condition (the repetition frequency and wavelength of irradiation light) of the light irradiation unit 110 and the position of the probe 180 by using the input unit 170.
  • the computer 150 may set a control parameter determined based on a user's instruction. Further, the computer 150 may move the probe 180 to a specified position by controlling the driving unit 130 based on the specified control parameter.
  • the drive unit 130 When imaging at a plurality of positions is designated, the drive unit 130 first moves the probe 180 to the first designated position. Note that the drive unit 130 may move the probe 180 to a position programmed in advance when a measurement start instruction is issued.
  • signal collecting section 140 When receiving the synchronization signal transmitted from light irradiating section 110, signal collecting section 140 starts the signal collecting operation. That is, the signal collecting unit 140 generates an amplified digital electric signal by amplifying and AD converting the analog electric signal derived from the photoacoustic wave output from the receiving unit 120, and outputs the amplified digital electric signal to the computer 150. .
  • the computer 150 stores the signal transmitted from the signal collecting unit 140. When imaging at a plurality of scanning positions is designated, the processes of S500 and S600 are repeatedly executed at the designated scanning positions, and irradiation of pulse light and generation of digital signals derived from acoustic waves are repeated. Note that the computer 150 may acquire and store the position information of the receiving unit 120 at the time of light emission based on the output from the position sensor of the drive unit 130 with the light emission as a trigger.
  • each of a plurality of wavelengths of light is radiated in a time-division manner.
  • the computer 150 as a photoacoustic image acquisition unit generates a photoacoustic image based on the stored signal data.
  • the computer 150 outputs the generated photoacoustic image to the storage device 1200 and stores it.
  • Reconstruction algorithms for converting signal data into a two-dimensional or three-dimensional spatial distribution include analytic reconstruction methods such as backprojection in the time domain and backprojection in the Fourier domain, and model-based methods (repetitive computations). Law) can be adopted.
  • a back-projection method in the time domain includes Universal back-projection (UBP), Filtered back-projection (FBP), or delay-and-sum (Delay-and-Sum).
  • the computer 150 generates initial sound pressure distribution information (sound pressures generated at a plurality of positions) as a photoacoustic image by performing a reconstruction process on the signal data. Further, the computer 150 calculates the optical fluence distribution of the light radiated on the subject 100 inside the subject 100, and divides the initial sound pressure distribution by the light fluence distribution to obtain the absorption coefficient distribution information by photoacoustic. It may be obtained as an image. A known method can be applied to the calculation method of the light fluence distribution. In addition, the computer 150 can generate a photoacoustic image corresponding to each of the light of a plurality of wavelengths.
  • the computer 150 can generate a first photoacoustic image corresponding to the first wavelength by performing a reconstruction process on signal data obtained by irradiating light of the first wavelength. Further, the computer 150 can generate a second photoacoustic image corresponding to the second wavelength by performing a reconstruction process on the signal data obtained by irradiating the second wavelength light. As described above, the computer 150 can generate a plurality of photoacoustic images corresponding to lights of a plurality of wavelengths.
  • the computer 150 acquires absorption coefficient distribution information corresponding to each of light of a plurality of wavelengths as a photoacoustic image.
  • the absorption coefficient distribution information corresponding to the first wavelength is defined as a first photoacoustic image
  • the absorption coefficient distribution information corresponding to the second wavelength is defined as a second photoacoustic image.
  • the present invention is also applicable to a system that does not include the photoacoustic apparatus 1100.
  • the present invention can be applied to any system as long as the image processing apparatus 1300 as a photoacoustic image acquisition unit can acquire a photoacoustic image.
  • the present invention can be applied to a system that does not include the photoacoustic device 1100 but includes the storage device 1200 and the image processing device 1300.
  • the image processing device 1300 as the photoacoustic image acquisition unit can acquire the photoacoustic image by reading out the specified photoacoustic image from the photoacoustic image group stored in the storage device 1200 in advance. it can.
  • the computer 150 as a spectral image acquisition unit generates a spectral image based on a plurality of photoacoustic images corresponding to a plurality of wavelengths.
  • the computer 150 outputs the spectral image to the storage device 1200 and causes the storage device 1200 to store the spectral image.
  • the computer 150 may generate, as a spectral image, an image indicating information corresponding to the concentration of a substance constituting the subject, such as glucose concentration, collagen concentration, melanin concentration, and volume fraction of fat and water. Good.
  • the computer 150 may generate, as a spectral image, an image representing a ratio between the first photoacoustic image corresponding to the first wavelength and the second photoacoustic image corresponding to the second wavelength.
  • a spectral image an image representing a ratio between the first photoacoustic image corresponding to the first wavelength and the second photoacoustic image corresponding to the second wavelength.
  • the computer 150 generates an oxygen saturation image as a spectral image according to Expression (1) using the first photoacoustic image and the second photoacoustic image.
  • the image processing apparatus 1300 as the spectral image acquisition unit may acquire a spectral image by reading out a specified spectral image from a group of spectral images stored in the storage device 1200 in advance.
  • the image processing apparatus 1300 as a photoacoustic image acquisition unit includes at least one of a plurality of photoacoustic images used to generate the read spectral image from a group of photoacoustic images stored in the storage device 1200 in advance. May be read to obtain a photoacoustic image.
  • the image processing device 1300 as a contrast agent information acquiring unit reads out a photoacoustic image or a spectral image from the storage device 1200 and acquires information about the contrast agent based on the photoacoustic image or the spectral image.
  • the image processing apparatus 1300 may execute image processing on the photoacoustic image or the spectral image, and calculate information on the contrast agent from the photoacoustic image or the spectral image. This makes it possible to acquire information on the contrast agent spread in the subject 100 from an image of the subject 100 with the contrast agent introduced into the subject 100.
  • the density of the contrast agent is estimated by image processing on the photoacoustic image when the absorption coefficient distribution image is a photoacoustic image and the image of the value of Expression (1) is a spectral image.
  • the user specifies the position of the desired contrast agent concentration in the photoacoustic image or the spectral image.
  • the image processing device 1300 acquires the image value of the photoacoustic image at the specified position.
  • the image processing apparatus 1300 refers to the absorption coefficient spectrum shown in FIG. 6 and acquires the absorption coefficient of each concentration of the contrast agent corresponding to the wavelength of the irradiation light.
  • the image processing apparatus 1300 can determine which type of contrast agent absorption coefficient to acquire based on the type of contrast agent acquired in S200. Then, the image processing apparatus 1300 compares the absorption coefficient of the contrast agent of each density with the image value of the photoacoustic image, and acquires the density of the contrast agent when the difference is small as information on the contrast agent. Note that the image processing apparatus 1300 calculates, as the information on the contrast agent, the density when the norm indicating the difference between the absorption coefficient of the contrast agent and the image value of the photoacoustic image becomes smaller than a predetermined value by the least square method. You may.
  • the image processing apparatus 1300 acquires an image value of a spectral image at a specified position.
  • the image processing apparatus 1300 refers to the absorption coefficient spectrum shown in FIG. 6 and acquires the absorption coefficient of each concentration of the contrast agent corresponding to two wavelengths of the irradiation light. Further, the image processing apparatus 1300 calculates a value corresponding to each density according to the equation (1) based on the absorption coefficient corresponding to each density. Then, the image processing apparatus 1300 compares the value of Expression (1) corresponding to each density with the image value of the spectral image, and acquires the density of the contrast agent when the difference is small as information on the contrast agent. . Note that the image processing apparatus 1300 uses the density when the norm indicating the difference between the calculated value of the equation (1) and the image value of the spectral image becomes smaller than a predetermined value by the least square method as information on the contrast agent. It may be calculated.
  • the computer 150 may read out information on the contrast agent stored as incidental information associated with the photoacoustic image or the spectral image and acquire information on the contrast agent.
  • the computer 150 can read the information about the contrast agent by reading the information about the contrast agent stored in the tag of the photoacoustic image or the spectral image as the DICOM image.
  • the image processing apparatus 1300 reads the image from the storage device 1200 such as the PACS and reads the image according to the condition of the contrast agent linked to the image. Display settings and wavelength settings can be made.
  • the image processing apparatus 1300 may read the type of the contrast agent from the supplementary information associated with the image, and calculate the density of the contrast agent by performing image processing on the image. As described above, the image processing apparatus 1300 may acquire a plurality of pieces of information on the contrast agent by a combination of different methods.
  • the image processing apparatus 1300 determines whether to reset the wavelength. If the image processing apparatus 1300 determines to reset the wavelength, the process returns to S400. If the image processing apparatus 1300 determines not to reset the wavelength, the process proceeds to S1100.
  • the image processing apparatus 1300 determines to reset the wavelength.
  • the image processing device 1300 may cause the display device 1400 to display information on the contrast agent acquired in S900.
  • the user may check the information displayed on the display device 1400 and, when it is determined that the wavelength needs to be reset, use the input device 1500 to give an instruction to reset the wavelength.
  • the image processing apparatus 1300 may determine that the wavelength is to be reset, and may cause the computer 150 to execute the wavelength reset.
  • the user may instruct the wavelength of the irradiation light itself as an instruction to reset the wavelength.
  • the image processing apparatus 1300 may compare the information on the contrast agent acquired in S200 with the information on the contrast agent acquired in S900, and determine that the wavelength is reset when there is a difference in the information.
  • the image processing apparatus 1300 may compare the information on the contrast agent acquired in S200 with the information on the contrast agent acquired in S900, and, if there is a difference in the information, display the fact on the display device 1400. In addition, the image processing apparatus 1300 may display what information about the contrast agent has what difference. The user may check the information displayed on the display device 1400 and, when determining that the wavelength needs to be reset, use the input device 1500 to give an instruction to reset the wavelength. That is, the image processing device 1300 may cause the display device 1400 to display information based on the information on the contrast agent acquired in S900.
  • the process advances to step S1100.
  • the image processing apparatus 1300 may determine that the wavelength has not been reset when an instruction to reset the wavelength is not received from the user for a certain period of time. Further, when receiving from the user an instruction indicating that the wavelength is not to be reset, the image processing apparatus 1300 may determine that the wavelength has not been reset. The image processing apparatus 1300 also determines that the wavelength has not been reset when there is no difference between the information on the contrast agent acquired in S200 and the information on the contrast agent acquired in S900. Good. If at least one of these conditions is received, the image processing apparatus 1300 may determine that the wavelength has not been reset.
  • the image processing apparatus 1300 as a display control unit displays the spectral image on the display device 1400 based on the information on the contrast agent acquired in S200 or S900 so that the region corresponding to the contrast agent and the other region can be identified. Let it.
  • a rendering method any method such as a maximum intensity projection (MIP), a volume rendering, and a surface rendering can be adopted.
  • MIP maximum intensity projection
  • volume rendering a volume rendering
  • surface rendering any method such as a maximum intensity projection (MIP), a volume rendering, and a surface rendering.
  • setting conditions such as a display area and a line-of-sight direction when rendering a three-dimensional image in two dimensions can be arbitrarily specified according to the observation target.
  • the image processing apparatus 1300 causes the GUI to display a color bar 2400 as a color scale indicating the relationship between the image value of the spectral image and the display color.
  • the image processing apparatus 1300 determines a numerical range of image values to be assigned to the color scale based on information on the contrast agent (for example, information indicating that the type of the contrast agent is ICG) and information indicating the wavelength of irradiation light. You may decide.
  • the image processing apparatus 1300 may determine a numerical range including a negative image value corresponding to an arterial oxygen saturation, a vein oxygen saturation, and a contrast agent according to equation (1).
  • the image processing apparatus 1300 may determine a numerical range of -100% to 100% and set a color bar 2400 in which -100% to 100% is assigned to a color gradation that changes from blue to red. With such a display method, in addition to the identification of the artery and vein, it is also possible to identify the area corresponding to the negative contrast agent. In addition, the image processing apparatus 1300 may cause the indicator 2410 indicating the numerical value range of the image value corresponding to the contrast agent to be displayed based on the information regarding the contrast agent and the information indicating the wavelength of the irradiation light.
  • a negative value area is indicated by an indicator 2410 as a numerical value range of an image value corresponding to ICG.
  • the image processing apparatus 1300 as the region determining means may determine a region corresponding to the contrast agent in the spectral image based on the information on the contrast agent and the information indicating the wavelength of the irradiation light. For example, the image processing apparatus 1300 may determine a region having a negative image value in the spectral image as a region corresponding to the contrast agent. Then, the image processing device 1300 may display the spectral image on the display device 1400 so that the region corresponding to the contrast agent and the other region can be identified.
  • the image processing apparatus 1300 displays an indicator (for example, a frame) indicating a region corresponding to the contrast agent, causing the display color of the region corresponding to the contrast agent to be different from that of the other region, blinking the region corresponding to the contrast agent, and the like.
  • An identification display such as display may be employed.
  • the display mode may be switched to a display mode for selectively displaying an image value corresponding to the ICG.
  • the image processing apparatus 1300 selects a voxel having a negative image value from the spectral image and selectively renders the selected voxel,
  • the ICG area may be selectively displayed.
  • the user may select an item 2710 corresponding to an artery display or an item 2720 corresponding to a vein display.
  • the image processing apparatus 1300 Based on a user's instruction, the image processing apparatus 1300 selectively selects an image value corresponding to an artery (for example, 90% or more and 100% or less) or an image value corresponding to a vein (for example, 60% or more and less than 90%).
  • the display mode may be switched to the display mode.
  • the numerical value range of the image value corresponding to the artery or the image value corresponding to the vein may be changeable based on a user's instruction.
  • hue, lightness, and saturation is assigned to the image value of the spectral image
  • an image in which the remaining parameters of hue, lightness, and saturation are assigned to the image value of the photoacoustic image is displayed as a spectral image.
  • an image in which hue and saturation are assigned to image values of a spectral image and brightness is assigned to image values of a photoacoustic image may be displayed as a spectral image.
  • the conversion table from the image value of the photoacoustic image to the brightness may be changed according to the image value of the spectral image. For example, when the image value of the spectral image is included in the numerical value range of the image value corresponding to the contrast agent, the brightness corresponding to the image value of the photoacoustic image may be smaller than that corresponding to the blood vessel.
  • the conversion table is a table indicating the brightness corresponding to each of the plurality of image values.
  • the image value of the spectral image is included in the numerical value range of the image value corresponding to the contrast agent, the brightness corresponding to the image value of the photoacoustic image may be larger than that corresponding to the blood vessel. That is, when the contrast agent region is compared with the blood vessel region, if the image value of the photoacoustic image is the same, the brightness of the contrast agent region may be greater than that of the blood vessel region.
  • the numerical value range of the image value of the photoacoustic image that does not convert the image value of the photoacoustic image into the brightness may differ depending on the image value of the spectral image.
  • the conversion table may be changed to a table suitable for the type and concentration of the contrast agent and the wavelength of the irradiation light. Therefore, the image processing apparatus 1300 may determine the conversion table from the image value of the photoacoustic image to the brightness based on the information regarding the contrast agent and the information indicating the wavelength of the irradiation light. If it is estimated that the image value of the photoacoustic image corresponding to the contrast agent is larger than that corresponding to the blood vessel, the image processing apparatus 1300 sets the brightness corresponding to the image value of the photoacoustic image corresponding to the contrast agent to the blood vessel. It may be smaller than the corresponding one.
  • the image processing apparatus 1300 may determine the brightness corresponding to the image value of the photoacoustic image corresponding to the contrast agent. May be larger than that corresponding to a blood vessel.
  • the GUI shown in FIG. 10 includes an absorption coefficient image (first photoacoustic image) 2100 corresponding to a wavelength of 797 nm, an absorption coefficient image (second photoacoustic image) 2200 corresponding to a wavelength of 835 nm, and an oxygen saturation image (spectral image) 2300. Is displayed.
  • the GUI may display which wavelength is generated by each image. In the present embodiment, both the photoacoustic image and the spectral image are displayed, but only the spectral image may be displayed.
  • the image processing device 1300 may switch between displaying a photoacoustic image and displaying a spectral image based on a user's instruction.
  • the display unit 160 may be capable of displaying a moving image.
  • the image processing apparatus 1300 generates at least one of the first photoacoustic image 2100, the second photoacoustic image 2200, and the spectral image 2300 in time series, and generates moving image data based on the generated time-series image. It may be configured to generate and output to the display unit 160.
  • the moving image display it is possible to repeatedly display a state in which lymph flows.
  • the speed of the moving image may be a predetermined speed specified in advance or a predetermined speed specified by the user.
  • the frame rate of the moving image be variable in the display unit 160 that can display the moving image.
  • a window for the user to manually input the frame rate, a slide bar for changing the frame rate, and the like may be added to the GUI of FIG.
  • the lymph fluid flows intermittently in the lymphatic vessels, only part of the acquired time-series volume data that can be used to confirm the lymph flow is used. Therefore, if real-time display is performed when checking the flow of lymph, efficiency may decrease. Therefore, by making the frame rate of the moving image displayed on the display unit 160 variable, the fast-moving display of the displayed moving image becomes possible, so that the user can confirm the state of the fluid in the lymphatic vessel in a short time. Become.
  • the display unit 160 may be capable of repeatedly displaying a moving image within a predetermined time range. At this time, it is also preferable to add a GUI such as a window or a slide bar for enabling the user to specify a range in which repeated display is performed, to FIG. This makes it easier for the user to grasp, for example, how the fluid flows in the lymphatic vessels.
  • a GUI such as a window or a slide bar
  • At least one of the image processing apparatus 1300 and the computer 150 as the information processing apparatus includes a spectral image acquisition unit, a contrast agent information acquisition unit, an area determination unit, a photoacoustic image acquisition unit, and a display control unit. It functions as a device having at least one.
  • each means may be comprised by mutually different hardware, and may be comprised by one hardware.
  • a plurality of units may be configured by one piece of hardware.
  • the blood vessel and the contrast agent can be distinguished by selecting a wavelength at which the value according to the formula (1) corresponding to the contrast agent is negative, but the image value corresponding to the contrast agent is a blood vessel.
  • the image value corresponding to the contrast agent may be any value as long as the image agent and the contrast agent can be identified.
  • the image processing described in this step can be applied to a case where the image value of the spectral image (oxygen saturation image) corresponding to the contrast agent becomes smaller than 60% or larger than 100%. .
  • the image processing according to the present embodiment may be applied to any contrast agent other than ICG. Further, the image processing apparatus 1300 may execute image processing according to the type of the contrast agent based on information on the type of the contrast agent introduced into the subject 100 among the plurality of types of contrast agents.
  • the case where the image processing method is determined based on the acquired information on the contrast agent among the information on the plurality of contrast agents has been described.
  • image processing corresponding to the condition of the contrast agent may be set in advance. Also in this case, the above-described image processing according to the present embodiment can be applied.
  • the image processing according to the present embodiment is applied to a photoacoustic image corresponding to one wavelength. May be. That is, the image processing apparatus 1300 determines a region corresponding to the contrast agent in the photoacoustic image based on the information regarding the contrast agent, and identifies the region corresponding to the contrast agent and the region other than the region. A photoacoustic image may be displayed. In addition, the image processing apparatus 1300 may display a spectral image or a photoacoustic image so that a region having a numerical value range of an image value corresponding to a preset contrast agent can be distinguished from other regions. .
  • the wavelength may be determined by the wavelength determining method according to the present embodiment. That is, the computer 150 may determine the wavelength of the irradiation light based on the information regarding the contrast agent. In this case, the computer 150 preferably determines a wavelength at which the image value of the region of the contrast agent in the photoacoustic image can be distinguished from the image value of the region of the blood vessel.
  • the light irradiating unit 110 may irradiate the subject 100 with light having a wavelength set in advance so that the image value of the contrast agent region in the photoacoustic image and the image value of the blood vessel region can be identified. Good. Further, the light irradiating unit 110 irradiates the subject 100 with light of a plurality of wavelengths set in advance so that the image value of the region of the contrast agent in the spectral image and the image value of the region of the blood vessel can be identified. Good.
  • the present invention is also realized by executing the following processing. That is, software (program) that realizes the functions of the above-described embodiments is supplied to a system or apparatus via a network or various storage media, and a computer (or CPU, MPU, or the like) of the system or apparatus reads the program and reads the program. This is the process to be performed.
  • Photoacoustic device 1200 Storage device 1300 Image processing device 1400 Display device 1500 Input device

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