WO2010095370A1 - Dispositif de diagnostic sur image et son procédé de commande - Google Patents

Dispositif de diagnostic sur image et son procédé de commande Download PDF

Info

Publication number
WO2010095370A1
WO2010095370A1 PCT/JP2010/000525 JP2010000525W WO2010095370A1 WO 2010095370 A1 WO2010095370 A1 WO 2010095370A1 JP 2010000525 W JP2010000525 W JP 2010000525W WO 2010095370 A1 WO2010095370 A1 WO 2010095370A1
Authority
WO
WIPO (PCT)
Prior art keywords
cross
unit
image
sectional image
body cavity
Prior art date
Application number
PCT/JP2010/000525
Other languages
English (en)
Japanese (ja)
Inventor
鬼村祐治
古市淳也
Original Assignee
テルモ株式会社
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by テルモ株式会社 filed Critical テルモ株式会社
Priority to JP2011500483A priority Critical patent/JP5628785B2/ja
Publication of WO2010095370A1 publication Critical patent/WO2010095370A1/fr

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6852—Catheters
    • 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
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/02007—Evaluating blood vessel condition, e.g. elasticity, compliance

Definitions

  • the present invention relates to an image diagnostic apparatus and a control method thereof.
  • OCT optical coherence tomography
  • the optical coherence tomography diagnostic apparatus emits measurement light into a blood vessel while rotating the optical mirror while a catheter containing an optical fiber having an optical lens and an optical mirror attached to the tip is inserted into the blood vessel. Radial scanning is performed by receiving the reflected light, and the cross-sectional image of the blood vessel based on the interference light is drawn by causing the reflected light obtained thereby to interfere with the reference light that has been divided from the measurement light in advance. is there.
  • optical coherence tomography diagnostic apparatus using wavelength sweeping has been developed as an improved version of the optical coherence tomography diagnostic apparatus.
  • optical coherence tomography diagnostic apparatus using wavelength sweep is the same as that of the optical coherence tomography diagnostic apparatus (OCT), but a light source having a wavelength longer than that of the optical coherence tomography diagnostic apparatus is used. Further, it is characterized in that light having different wavelengths is continuously emitted. In addition, a mechanism for changing the optical path length of the reference light is not required by obtaining the reflected light intensity at each point in the depth direction of the living tissue by frequency analysis of the interference light.
  • optical coherence tomographic image diagnostic apparatus OCT
  • optical coherent tomographic image diagnostic apparatus OFDI
  • the interference light used in such a diagnostic imaging apparatus has a wavelength of about 800 nm to 1550 nm and is impermeable to blood. For this reason, when rendering a cross-sectional image of a blood vessel, it is necessary to remove blood in the blood vessel in advance from the region to be rendered.
  • Examples of the method for removing blood in the blood vessel at the site to be imaged include occlusion, flushing with physiological saline, lactated Ringer, contrast agent, etc. Since this is a heavy burden on the patient, it is desirable that the operation for drawing the cross-sectional image be performed with minimal invasiveness.
  • the blood flow velocity and blood flow volume are originally different among individuals, and the speed and amount of flushing vary depending on the shape of the coronary artery entrance. For this reason, even if the blood removal operation in the blood vessel is performed in the same manner, there are individual differences in the degree of removal.
  • the cross-sectional image drawn due to the influence of the blood remaining in the blood vessel The image quality of the image is significantly deteriorated, and in some cases, the image quality may be deteriorated so as not to be observed. Moreover, even if the blood remaining in the blood vessel is small, a decrease in luminance is unavoidable, which may cause a misdiagnosis.
  • the pullback is started after confirming the removal of blood in the blood vessel is completed, and only the cross-sectional image after the start of the pullback is stored and used for diagnosis.
  • the configuration is such that a pull-back start instruction and a cross-sectional image storage instruction are input when the user completes, The workload is high.
  • the intensity of reflected light from one direction (the emission direction of the measurement light when the optical mirror stops rotating scanning) at the start of radial scanning and sectional image storage operations. Is used to determine whether or not blood removal has been completed. For this reason, when there is a guide wire used for optical probe insertion in the measurement light emission direction, or when the measurement light emission port and the blood vessel wall are in close contact with each other, there is almost no blood between the optical probe and the blood vessel wall.
  • the degree of blood removal in the blood vessel is not uniform in the circumferential direction, it cannot be determined with high accuracy whether blood removal in the blood vessel has been completed, and a stored cross-sectional image is displayed. A cross-sectional image with degraded image quality or a cross-sectional image including the cause of misdiagnosis is included.
  • the present invention has been made in view of the above problems, and it is an object of the present invention to reduce the work load of a user when rendering a cross-sectional image in an image diagnostic apparatus and to eliminate the cause of image quality deterioration and misdiagnosis of the cross-sectional image.
  • an image diagnostic apparatus comprises the following arrangement. That is, By connecting a probe having a transmission / reception unit that continuously transmits and receives light, and moving the inside of the body cavity in the axial direction while rotating and scanning the transmission / reception unit, the reflected light in the body cavity is obtained from the transmission / reception unit, An image diagnostic apparatus that generates and displays a plurality of cross-sectional images in the axial direction in the body cavity based on the acquired reflected light, The presence / absence of body fluid in the body cavity is determined using cross-sectional image data generated based on the reflected light acquired from the transmission / reception unit in a state where axial movement is stopped and rotationally scanned in the body cavity. Calculating means for calculating an evaluation value for When the evaluation value calculated by the calculation unit satisfies a predetermined condition, the unit includes an instruction unit that issues a start instruction for starting acquisition of a cross-sectional image used for diagnosis.
  • the present invention it is possible to reduce the work load on the user when rendering a cross-sectional image in the image diagnostic apparatus, and to eliminate the cause of image quality deterioration and misdiagnosis of the cross-sectional image.
  • FIG. 1A is a diagram illustrating an external configuration of an image diagnostic apparatus.
  • FIG. 1B is a diagram illustrating a configuration of a tip portion of the optical probe portion.
  • FIG. 2 is a diagram illustrating a functional configuration of the optical coherence tomographic image diagnostic apparatus 100.
  • FIG. 3 is a diagram illustrating a functional configuration of the optical coherence tomographic image diagnosis apparatus 100 using wavelength sweeping.
  • FIG. 4 is a diagram illustrating a detailed configuration of the signal processing unit and related functional blocks in the first embodiment.
  • FIG. 5 is a diagram illustrating an example of the generated cross-sectional image.
  • FIG. 6 is a diagram illustrating an example of the designated ROI.
  • FIG. 7 is a flowchart showing the flow of the operation start determination process.
  • FIG. 8 is a diagram illustrating a detailed configuration of the signal processing unit and related functional blocks in the second embodiment.
  • FIG. 9 is a flowchart showing the flow of the operation start determination process.
  • FIG. 10 is a flowchart showing the flow of the operation end determination process.
  • FIG. 1A is a diagram showing an external configuration of an image diagnostic apparatus (an optical coherent tomographic image diagnostic apparatus or an optical coherent tomographic image diagnostic apparatus using wavelength sweep) 100 according to the first embodiment of the present invention.
  • the diagnostic imaging apparatus 100 includes an optical probe unit 101, a scanner / pullback unit 102, and an operation control device 103.
  • the scanner / pullback unit 102 and the operation control device 103 are connected to a signal line 104. Connected by.
  • the optical probe unit 101 is inserted directly into the blood vessel and measures the state inside the blood vessel using the imaging core 130.
  • the scanner / pullback unit 102 can be attached to and detached from the optical probe unit 101, has a built-in motor, and defines the radial operation of the imaging core 130 in the optical probe unit 101.
  • the operation control device 103 has a function for inputting various setting values and a function for processing data obtained by measurement and displaying it as a cross-sectional image when performing intravascular optical coherence tomography diagnosis.
  • reference numeral 111 denotes a main body control unit that processes data obtained by measurement and outputs a processing result.
  • Reference numeral 111-1 denotes a printer / DVD recorder, which prints a processing result in the main body control unit 111 or stores it as data.
  • Reference numeral 113 denotes an LCD monitor as a display device, which displays a processing result in the main body control unit 111.
  • an imaging core 130 including a housing 131 in which a transmission / reception unit 133 that transmits and receives measurement light is disposed inside a lumen of the catheter sheath 121 and a drive shaft 132 that transmits a driving force for rotating the housing 131.
  • a transmission / reception unit 133 that transmits and receives measurement light is disposed inside a lumen of the catheter sheath 121 and a drive shaft 132 that transmits a driving force for rotating the housing 131.
  • the transmission / reception unit 133 incorporates a mirror that reflects the optical axis of the measurement light transmitted by the optical fiber inserted through the drive shaft 132 to the side.
  • the transmission / reception unit 133 transmits the measurement light toward the tissue in the body cavity and receives the reflected light from the tissue in the body cavity.
  • the drive shaft 132 is formed in a coil shape, and a signal line (single mode fiber) is arranged inside thereof.
  • the housing 131 has a shape having a notch in a part of a short cylindrical metal pipe, and is formed by cutting out from a metal lump or MIM (metal powder injection molding).
  • the housing 131 has a transmission / reception unit 133 inside, and the base end side is connected to the drive shaft 132.
  • a short coil-shaped elastic member 123 is provided on the tip side.
  • the elastic member 123 is made of a stainless steel wire formed in a coil shape, and the elastic member 123 is arranged on the distal end side, so that stability during rotation of the imaging core 130 is improved.
  • 124 is a reinforcing coil, and is provided for the purpose of preventing a sudden bending of the distal end portion of the catheter sheath 121.
  • the guide wire lumen tube 122 has a guide wire lumen into which a guide wire can be inserted.
  • the guide wire lumen tube 122 is used to receive a guide wire previously inserted into the body cavity and guide the catheter sheath 121 to the affected area by the guide wire.
  • the drive shaft 132 is capable of rotating and axially moving with respect to the catheter sheath 121, has a characteristic of being flexible and capable of transmitting rotation well, for example, a multi-layered close contact coil made of a metal wire such as stainless steel. Etc.
  • the low-coherence light source 209 is a low-interference light source such as an ultra-bright light emitting diode.
  • the low-coherence light source 209 outputs low-coherence light that exhibits coherence only in a short distance range where the wavelength is about 1310 nm and the coherence distance (coherent length) is about several ⁇ m to several tens of ⁇ m. .
  • the difference between the two optical path lengths from the divided point to the mixed point is within a short distance range of about several ⁇ m to several tens of ⁇ m. Is detected as interference light, and is not detected as interference light when the optical path length difference is larger than that.
  • the light of the low-coherence light source 209 is incident on one end of the first single mode fiber 228 and transmitted to the tip surface side.
  • the first single mode fiber 228 is optically coupled to the second single mode fiber 229 and the third single mode fiber 232 at an intermediate optical coupler unit 208.
  • the optical coupler unit is an optical component that can divide one optical signal into two or more outputs, or combine two or more input optical signals into one output, and has low interference.
  • the light from the light source 209 can be transmitted by being divided into a maximum of three optical paths by the optical coupler unit 208.
  • a scanner / pullback unit 102 is provided on the distal end side of the optical coupler unit 208 of the first single mode fiber 228.
  • an optical rotary joint 203 that couples the non-rotating unit and the rotating unit and transmits light is provided.
  • the distal end side of the fourth single mode fiber 230 in the optical rotary joint 203 is detachably connected to the fifth single mode fiber 231 of the optical probe unit 101 via the adapter 202.
  • light from the low-coherence light source 209 is transmitted to the fifth single mode fiber 231 that is inserted into the imaging core 201 (corresponding to reference numeral 130 in FIG. 1B) that repeatedly transmits and receives light and that can be driven to rotate. .
  • the light transmitted to the fifth single mode fiber 231 is irradiated from the distal end side of the imaging core 201 to the living tissue in the blood vessel while performing radial scanning. Then, a part of the reflected light scattered on the surface or inside of the living tissue is taken in by the imaging core 201, returns to the first single mode fiber 228 side through the reverse optical path, and a part of the reflected light is reflected by the optical coupler unit 208. 2 moves to the single mode fiber 229 side. And it is radiate
  • the photodetector for example, photodiode 210.
  • the rotating part side of the optical rotary joint 203 is rotationally driven by a radial scanning motor 205 of a rotational driving device 204.
  • the rotation angle of the radial scanning motor 205 is detected by the encoder unit 206.
  • the scanner / pullback unit 102 includes a linear drive device 207, and moves in the axial direction (the distal direction in the body cavity and the opposite direction) of the imaging core 201 based on an instruction from the signal processing unit 214 (axial operation). ).
  • the axial movement is realized by the linear drive device 207 moving the scanner including the optical rotary joint 203 based on a control signal from the signal processing unit 214.
  • the catheter sheath of the optical probe unit 101 remains fixed in the blood vessel, and only the imaging core 201 stored in the catheter sheath moves in the axial direction, so that the axial operation can be performed without damaging the blood vessel wall. Done.
  • an optical path length variable mechanism 216 that changes the optical path length of the reference light is provided on the tip side (reference optical path) of the optical coupler unit 208 of the second single mode fiber 229.
  • This optical path length variable mechanism 216 replaces the optical probe unit 101 with first optical path length changing means that changes the optical path length corresponding to the examination range in the depth direction of the living tissue (the direction in which the measurement light is emitted) at high speed. And second optical path length changing means for changing the optical path length corresponding to the variation in length so as to be able to absorb variations in length of the individual optical probe sections 101 when used.
  • a grating 219 is arranged via a collimating lens 221 that is mounted on the uniaxial stage 220 together with the tip of the second single mode fiber 229 and that is movable in the direction indicated by the arrow 223. Further, a galvanometer 217 capable of turning by a minute angle is attached as a first optical path length changing means via a lens 218 corresponding to the grating 219 (diffraction grating). The galvanometer 217 is rotated at high speed in the direction of the arrow 222 by the galvanometer controller 224.
  • the galvanometer 217 reflects light by a mirror of the galvanometer, and is configured to rotate the mirror attached to the movable part at high speed by applying an AC drive signal to the galvanometer functioning as a reference mirror.
  • a drive signal is applied from the galvanometer controller 224 to the galvanometer 217, and the optical signal is rotated in the direction of the arrow 222 at a high speed by the drive signal, so that the optical path length of the reference light is within the examination range in the depth direction of the living tissue. It will change at high speed by the corresponding optical path length.
  • One period of the change in the optical path difference is a period for acquiring interference light for one line.
  • the uniaxial stage 220 functions as a second optical path length changing unit having a variable range of the optical path length that can absorb the variation in the optical path length of the optical probe unit 101. Further, the uniaxial stage 220 also has a function as an adjusting means for adjusting the offset. For example, even when the tip of the optical probe unit 101 is not in close contact with the surface of the living tissue, the optical path length is minutely changed by the uniaxial stage 220, thereby setting the state to interfere with the reflected light from the surface position of the living tissue. It becomes possible to do.
  • the light whose optical path length has been changed by the optical path length variable mechanism 216 is mixed with the light obtained from the first single mode fiber 228 side by the optical coupler unit 208 provided in the middle of the second single mode fiber 229. It is received by the photodiode 210 as interference light.
  • the interference light received by the photodiode 210 in this way is photoelectrically converted and amplified by the amplifier 211.
  • the signal is input to the demodulator 212, and the demodulator 212 performs demodulation processing for extracting only the signal portion of the interfered light, and the output is input to the A / D converter 213.
  • the A / D converter 213 samples the interference light signal for 200 points, for example, and generates one line of digital data (“interference light data”).
  • the sampling frequency is a value obtained by dividing the time of one scanning of the optical path length by 200.
  • the line-by-line interference light data generated by the A / D converter 213 is input to the signal processing unit 214.
  • the signal processing unit 214 converts the interference light data in the depth direction of the living tissue into a video signal, thereby forming a cross-sectional image at each position in the blood vessel, and the LCD monitor 215 (see FIG. 1) at a predetermined frame rate. (Corresponding to number 113).
  • the signal processing unit 214 is further connected to the optical path length adjusting means control device 226.
  • the signal processing unit 214 controls the position of the uniaxial stage 220 via the optical path length adjusting unit controller 226.
  • the signal processing unit 214 is connected to the motor control circuit 225 and controls the rotational drive of the radial scanning motor 205.
  • the signal processing unit 214 is connected to a galvanometer controller 224 that controls scanning of the optical path length of the reference mirror (galvanometer mirror), and the galvanometer controller 224 outputs a drive signal to the signal processing unit 214.
  • the motor control circuit 225 synchronizes with the galvanometer controller 224 based on this drive signal.
  • FIG. 3 is a diagram showing a functional configuration of the optical coherence tomography diagnostic apparatus 100 using wavelength sweep.
  • the difference from the optical coherence tomographic image diagnosis apparatus described with reference to FIG. 2 will be mainly described.
  • a wavelength swept light source 308 using a sweep laser is a type of extended-cavity laser that includes an optical fiber 316 and a polygon scanning filter (308b) coupled in a ring shape with an SOA 315 (semiconductor optical amplifier).
  • the light output from the SOA 315 travels through the optical fiber 316 and enters the polygon scanning filter 308b.
  • the light whose wavelength is selected here is amplified by the SOA 315 and finally output from the coupler 314.
  • the wavelength is selected by a combination of the diffraction grating 312 for separating light and the polygon mirror 309.
  • the light split by the diffraction grating 312 is condensed on the surface of the polygon mirror 309 by two lenses (310, 311).
  • the wavelength mirror can be swept in time by rotating the polygon mirror 309. .
  • the polygon mirror 309 for example, a 32-hedron mirror is used, and the rotation speed is about 50000 rpm. High speed and high output wavelength sweeping is possible by a unique wavelength sweeping method combining the polygon mirror 309 and the diffraction grating 312.
  • the light of the wavelength swept light source 308 output from the Coupler 314 is incident on one end of the first single mode fiber 330 and transmitted to the distal end side.
  • the first single mode fiber 330 is optically coupled to the second single mode fiber 337 and the third single mode fiber 331 at an intermediate optical coupler unit 334. Accordingly, the light incident on the first single mode fiber 330 is divided into a maximum of three optical paths by the optical coupler unit 334 and transmitted.
  • An optical rotary joint 303 that couples the non-rotating part and the rotating part and transmits light is provided on the tip side of the optical coupler part 334 of the first single mode fiber 330.
  • the distal end side of the fourth single mode fiber 335 in the optical rotary joint 303 is detachably connected to the fifth single mode fiber 336 of the optical probe unit 101 via the adapter 302.
  • light from the wavelength swept light source 308 is transmitted to the fifth single mode fiber 336 that is inserted into the imaging core 301 (corresponding to reference numeral 130 in FIG. 1B) and can be driven to rotate.
  • the transmitted light is irradiated from the distal end side of the imaging core 301 to the living tissue in the body cavity while performing radial scanning.
  • a part of the reflected light scattered on the surface or inside of the living tissue is taken in by the imaging core 301 and returns to the first single mode fiber 330 side through the reverse optical path.
  • a part of the optical coupler unit 334 moves to the second single mode fiber 337 side, is emitted from one end of the second single mode fiber 337, and is received by a photodetector (eg, a photodiode 319).
  • the rotating portion side of the optical rotary joint 303 is rotationally driven by the radial scanning motor 305 of the rotational driving device 304. Further, the rotation angle of the radial scanning motor 305 is detected by the encoder unit 306. Further, the scanner / pullback unit 102 includes a linear drive device 307 and regulates the axial operation of the imaging core 301 based on an instruction from the signal processing unit 323.
  • an optical path length variable mechanism 325 for finely adjusting the optical path length of the reference light is provided on the tip side of the optical coupler section 334 of the second single mode fiber 337.
  • the optical path length variable mechanism 325 changes the optical path length corresponding to the variation in length so that the variation in length of each optical probe unit 101 when the optical probe unit 101 is replaced and used can be absorbed.
  • Optical path length changing means is provided.
  • the third single mode fiber 331 and the collimating lens 326 are provided on a uniaxial stage 332 that is movable as indicated by an arrow 333 in the optical axis direction, and form optical path length changing means.
  • the uniaxial stage 332 functions as an optical path length changing unit having a variable range of the optical path length that can absorb the variation in the optical path length of the optical probe unit 101. Further, the uniaxial stage 332 also has a function as an adjusting means for adjusting the offset. For example, even when the tip of the optical probe unit 101 is not in close contact with the surface of the living tissue, the optical path length is minutely changed by the uniaxial stage, thereby setting the state to interfere with the reflected light from the surface position of the living tissue. It becomes possible.
  • the light whose optical path length is finely adjusted by the optical path length variable mechanism 325 is mixed with the light obtained from the first single mode fiber 330 side by the optical coupler unit 334 provided in the middle of the third single mode fiber 331.
  • the light is received by the photodiode 319.
  • the interference light received by the photodiode 319 in this way is photoelectrically converted, amplified by the amplifier 320, and then input to the demodulator 321.
  • the demodulator 321 performs demodulation processing for extracting only the signal portion of the interfered light, and its output is input to the A / D converter 322 as an interference light signal.
  • the A / D converter 322 samples the interference light signal for 2048 points at 180 MHz, for example, and generates one line of digital data (interference light data).
  • the sampling frequency of 180 MHz is based on the assumption that about 90% of the wavelength sweep period (12.5 ⁇ sec) is extracted as 2048 digital data when the wavelength sweep repetition frequency is 40 kHz.
  • the present invention is not limited to this.
  • the line-by-line interference light data generated by the A / D converter 322 is input to the signal processing unit 323.
  • the signal processing unit 323 In the measurement mode, the signal processing unit 323 generates a depth direction data by frequency-resolving the interference light data by FFT (Fast Fourier Transform), and converts the cross-section at each position in the blood vessel. An image is formed and output to an LCD monitor 317 (corresponding to reference numeral 113 in FIG. 1) at a predetermined frame rate.
  • FFT Fast Fourier Transform
  • the signal processing unit 323 is further connected to the optical path length adjusting means control device 318.
  • the signal processing unit 323 controls the position of the uniaxial stage 332 via the optical path length adjusting unit control device 318.
  • the signal processing unit 323 is connected to the motor control circuit 324 and receives a video synchronization signal from the motor control circuit 324.
  • the signal processing unit 323 forms a cross-sectional image in synchronization with the received video synchronization signal.
  • the video synchronization signal of the motor control circuit 324 is also sent to the rotation drive device 304, and the rotation drive device 304 outputs a drive signal synchronized with the video synchronization signal.
  • FIG. 4 is a diagram illustrating a detailed configuration of the signal processing units 214 and 323 and related functional blocks.
  • the interference light data generated by the A / D converters 213 and 322 is output from the encoder 206 or 306 of the radial scanning motor 205 or 305 output from the motor control circuit 225 or 324 in the line memory unit 401. After being processed so that the number of lines per rotation of the radial scanning motor is 512, it is output to the subsequent line data generation unit 402.
  • the line data generation unit 402 generates line data by performing line addition averaging processing, filtering processing, logarithmic conversion processing, and the like on the interference light data, and generating interference light intensity data in the depth direction of the living tissue. Thereafter, the generated line data is output to the signal post-processing unit 403 at the subsequent stage.
  • the signal post-processing unit 403 performs contrast adjustment, luminance adjustment, gamma correction, frame correlation, sharpness processing, and the like on the line data, and outputs the result to the image construction unit (DSC) 404.
  • DSC image construction unit
  • the image construction unit 404 generates a cross-sectional image by performing R ⁇ conversion on the polar coordinate line data string, and then converts it into a video signal, and displays the cross-sectional image on the LCD monitor 215 or 317.
  • a cross-sectional image is generated from 512 lines as an example, but the number of lines is not limited to this.
  • the determination area setting unit 406 sets an area on the cross-sectional image corresponding to the determination area (ROI) designated by the user via the operation panel 112 in the operation start determination unit 405.
  • the operation start determination unit 405 determines whether to start a predetermined operation based on the luminance value of the image data specified by the region set by the determination region setting unit 406 among the cross-sectional images generated by the image construction unit 404. An evaluation value for determining whether or not is calculated. In the operation start determination unit 405, when the calculated evaluation value satisfies a predetermined condition, a predetermined operation (operation for storing the cross-sectional image generated in the image construction unit 404 in the memory 408 in the control unit 407) is started. An instruction is given to the control unit 407.
  • the control unit 407 controls the operation of each unit and stores the cross-sectional image generated by the image construction unit 404 in the memory 408 based on the start instruction from the operation start determination unit 405.
  • the operation start determination unit 405 and the determination region setting unit 406 are illustrated as different functional blocks from the control unit 407, but are realized by software as one function of the control unit 407. Needless to say, it may be configured as described above.
  • FIG. 5 is a diagram illustrating an example of a cross-sectional image generated by the image construction unit 404 in a state where the imaging core 201 or 301 stops the axial movement and is rotationally scanned.
  • reference numeral 501 denotes the housing 131 or catheter sheath 121 of the imaging core 201 or 301
  • 502 denotes the inner wall of the blood vessel
  • 503 denotes a guide wire used for insertion of the optical probe unit 101.
  • a region inside the inner wall 502 of the blood vessel and excluding the region 501 of the optical probe unit 101 is designated as a determination region (ROI) via the operation panel 112, Based on the luminance value of the image data on the cross-sectional image corresponding to the specified determination region (ROI), it is determined whether or not to start the operation of saving the cross-sectional image in the memory 408 in the control unit 407.
  • ROI determination region
  • FIG. 6 is a diagram illustrating an example of a determination area specified via the operation panel 112.
  • reference numeral 502 denotes an inner wall of a blood vessel
  • reference numeral 501 denotes an optical probe housing.
  • a region indicated by hatching indicates a determination region (ROI).
  • FIG. 6A shows a state in which the entire cross-sectional image in the blood vessel excluding the region 501 of the optical probe unit 101 is designated as the determination region.
  • FIG. 6 shows a state in which a predetermined angle in the circumferential direction is designated as the determination region in the cross-sectional image in the blood vessel excluding the region 501 of the optical probe unit 101.
  • 6C shows a state in which a predetermined circular region is designated as a determination region in the cross-sectional image in the blood vessel excluding the region 501 of the optical probe unit 101, and 6D in FIG. A state in which a predetermined rectangular area is designated as a determination area among the cross-sectional images in the blood vessel excluding the area 501 is shown.
  • FIG. 6 shows a state in which a plurality of specified rectangular areas are designated as determination areas among cross-sectional images in the blood vessel excluding the area 501 of the optical probe unit 101.
  • FIG. 6 shows a state in which a predetermined circular region around the region 501 of the optical probe unit 101 and the region 501 of the optical probe unit 101 is designated as a determination region in the tomographic image in the blood vessel.
  • FIG. 6G in FIG. 6 shows that a predetermined circular region around the region 501 of the optical probe unit 101 is designated as the determination region in the tomographic image in the blood vessel excluding the region 501 of the optical probe unit 101 in the tomographic image in the blood vessel. Is shown.
  • an evaluation value used for the operation start determination process in the operation start determination unit 405 is calculated based on the luminance value of the image data corresponding to the determination region.
  • the sum of luminance values of image data corresponding to the determination area is used as the calculated evaluation value.
  • the present invention is not limited to this.
  • an average value of luminance values of image data corresponding to the determination region may be used as the evaluation value.
  • the standard deviation of the luminance value distribution of the image data corresponding to the determination area may be used as the evaluation value.
  • a determination area setting unit 406 for setting an area on the cross-sectional image corresponding to the determination area (ROI) designated by the user via the operation panel 112 in the operation start determination unit 405 the operation is not performed. It goes without saying that a determination region (ROI) used in the start determination unit may be set in advance and used for operation start determination.
  • FIG. 7 is a flowchart showing the flow of the operation start determination process in the operation start determination unit 405 and the determination region setting unit 406. Note that the flowchart shown in FIG. 7 is executed in a state where the axial movement of the imaging core 130 is stopped in the blood vessel and rotational scanning is performed.
  • step S701 the determination region setting unit 406 identifies the determination region designated via the operation panel 112, and sets the region on the cross-sectional image used for calculation of the evaluation value in the operation start determination unit 405.
  • step S ⁇ b> 702 the operation start determination unit 405 acquires the cross-sectional image generated by the image construction unit 404.
  • step S703 an evaluation value is calculated using the luminance value of the image data specified by the region set in step S701 among the cross-sectional images acquired in step S702.
  • step S704 it is determined whether or not the evaluation value calculated in step S703 is equal to or less than a predetermined threshold value. Note that a predetermined fixed value is used as the threshold used at this time.
  • a cross-sectional image before the flash is acquired in advance, and the brightness value of the image data on the cross-sectional image corresponding to the determination region of the cross-sectional image before the flash You may make it use the value obtained by integrating
  • step S704 If it is not determined in step S704 that the evaluation value is equal to or less than the threshold value, it is determined that blood remains in the blood vessel, the process returns to step S702, and the same process is repeated by acquiring the next cross-sectional image. . On the other hand, if it is determined in step S704 that the evaluation value is equal to or less than the threshold value, it is determined that no blood remains in the blood vessel, and the process proceeds to step S705.
  • step S705 an operation start instruction is issued to the control unit 407.
  • the control unit 407 receives the operation start instruction, the control unit 407 starts an operation of storing the cross-sectional image generated by the image construction unit 404 in the memory. Thereby, a cross-sectional image used for diagnosis is acquired.
  • the presence or absence of blood is determined based on the luminance value of the image data corresponding to the predetermined determination region of the generated cross-sectional image.
  • the storage operation of the generated cross-sectional image in the memory is started.
  • the operation start determination is performed based on the image data on the cross-sectional image generated by the image construction unit (DSC) 404, but the present invention is not limited to this.
  • the image construction unit (DSC) 404 may be configured to perform the operation start determination based on line data before R ⁇ conversion in order to generate a cross-sectional image.
  • FIG. 8 is a diagram showing a detailed configuration of the signal processing units 214 and 323 of the image diagnostic apparatus 100 (optical coherence tomographic image diagnostic apparatus or optical coherence tomographic image diagnostic apparatus using wavelength sweep) according to the second embodiment of the present invention. It is.
  • the operation start determination unit 805 is configured to operate based on the output from the signal post-processing unit 403.
  • the determination region setting unit 806 sets a range on the line data corresponding to the determination region (ROI) designated by the user via the operation panel 112 in the operation start determination unit 805.
  • the operation start determination unit 805 calculates an evaluation value based on the sum or average value of the signal values of the line data specified by the range set in the determination region setting unit 806 among the line data before R ⁇ conversion, An operation start instruction is issued to the control unit 407 based on the calculated evaluation value.
  • the operation start determination unit 805 and the determination region setting unit 806 are illustrated as different functional blocks from the control unit 407, but are realized by software as one function of the control unit 407. Needless to say, it may be configured as described above.
  • FIG. 9 is a flowchart showing the flow of operation start determination processing in the operation start determination unit 805 and the determination area setting unit 806. Note that the flowchart shown in FIG. 9 is executed in a state where the axial movement of the imaging core 130 is stopped in the blood vessel and rotational scanning is performed.
  • step S901 the determination region setting unit 806 identifies the determination region designated via the operation panel 112, and sets the range on the line data used for calculating the evaluation value in the operation start determination unit 805.
  • step S902 the operation start determination unit 805 acquires line data generated by the signal post-processing unit 403.
  • step S903 an evaluation value is calculated using the signal value of the line data specified by the range set in step S901 among the line data acquired in step S902.
  • step S904 it is determined whether or not the evaluation value calculated in step S903 is equal to or less than a predetermined threshold value. Note that a predetermined fixed value is used as the threshold used at this time.
  • the present invention is not limited to this.
  • line data in a state before the flash is acquired in advance, and signal values of the line data corresponding to the determination area among the line data in the state before the flash are used.
  • a value obtained by adding a predetermined coefficient to the calculated evaluation value may be used as the threshold value.
  • step S904 If it is not determined in step S904 that the evaluation value is equal to or less than the threshold value, it is determined that blood remains in the blood vessel, the process returns to step S902, and the same processing is repeated by acquiring the next line data. . On the other hand, if it is determined in step S904 that the evaluation value is equal to or less than the threshold value, it is determined that no blood remains in the blood vessel, and the process proceeds to step S905.
  • step S905 an operation start instruction is issued to the control unit 407.
  • the control unit 407 receives the operation start instruction, the control unit 407 starts an operation of storing the cross-sectional image generated by the image construction unit 404 in the memory. Thereby, a cross-sectional image used for diagnosis is acquired.
  • the presence or absence of blood is determined based on the signal value of the line data corresponding to the determination region in the generated line data, and blood remains.
  • the storage operation of the generated cross-sectional image in the memory is started.
  • the operation start instruction to be performed when the evaluation value is equal to or less than the threshold value is configured to issue an instruction to start storing the generated cross-sectional image in the memory.
  • the present invention is not limited to this.
  • a pull back start instruction may be issued together with an instruction to start storing the cross-sectional image in the memory.
  • FIG. 10 is a flowchart showing the flow of the operation end determination process.
  • 10A in FIG. 10 is a flowchart in the case where the operation end determination is performed based on the cross-sectional image generated in the image construction unit 404.
  • step S1001 the determination region setting unit 406 identifies the determination region designated via the operation panel 112, and sets the region on the cross-sectional image used for calculating the evaluation value in the operation start determination unit 405.
  • step S ⁇ b> 1002 the operation start determination unit 405 acquires the cross-sectional image generated by the image construction unit 404.
  • step S1003 an evaluation value is calculated using the luminance value of the image data specified by the region set in step S1001 among the cross-sectional images acquired in step S1002.
  • step S1004 it is determined whether or not the evaluation value calculated in step S1003 is larger than a predetermined threshold value. Note that a predetermined fixed value is used as the threshold used at this time.
  • a cross-sectional image before the flash is acquired in advance, and the brightness value of the image data on the cross-sectional image corresponding to the determination region of the cross-sectional image before the flash You may make it use the value obtained by integrating
  • step S1004 If it is determined in step S1004 that the evaluation value is equal to or less than the threshold value, it is determined that blood has not flowed into the blood vessel, the process returns to step S1002, and the same processing is repeated by acquiring the next cross-sectional image. . On the other hand, if it is determined in step S1004 that the evaluation value is greater than the threshold value, it is determined that blood has flowed into the blood vessel, and the process proceeds to step S1005.
  • step S1005 an operation end instruction is issued to the control unit 407.
  • the control unit 407 ends the operation of storing the cross-sectional image generated by the image construction unit 404 in the memory.
  • FIG. 10 is a flowchart in the case of outputting an operation end instruction when a predetermined time has elapsed after the operation start determination.
  • step S1011 the operation start timing is recognized based on the output of the operation start instruction.
  • step S1012 it is determined whether a predetermined time has elapsed from the operation start timing.
  • step S1012 when it is determined that the predetermined time has not elapsed since the operation start timing, the process waits until the predetermined time elapses. On the other hand, if it is determined in step S1012 that the predetermined time has elapsed, the process proceeds to step S1013.
  • step S1013 an operation end instruction is issued to the control unit 407.
  • the control unit 407 ends the operation of storing the cross-sectional image generated by the image construction unit 404 in the memory.
  • 10C in FIG. 10 is a flowchart for outputting an operation end instruction when the data amount of the cross-sectional image stored in the memory 408 in the control unit 407 reaches a predetermined data amount.
  • step S1021 the operation start timing is recognized based on the output of the operation start instruction.
  • step S1022 monitoring of memory usage is started.
  • step S1023 it is determined whether or not the memory usage amount in the control unit 407 has reached a predetermined amount or more. If it is determined in step S1023 that the amount is not greater than the predetermined amount, the operation of saving the cross-sectional image in the memory is continued.
  • step S1023 determines whether the amount exceeds the predetermined amount. If it is determined in step S1023 that the amount exceeds the predetermined amount, the process proceeds to step S1023, and an operation end instruction is issued to the control unit 407.
  • the control unit 407 ends the operation of storing the cross-sectional image generated by the image construction unit 404 in the memory.
  • the present embodiment is configured to automatically determine whether the operation has ended. As a result, according to the present embodiment, it is possible to further reduce the user's work load.
  • the operation end instruction is configured to instruct the control unit to end the storage operation in the memory.
  • the present invention is not limited to this, and the save operation end instruction is issued together with the pull back end instruction. You may comprise as follows.
  • the pullback is ended at an appropriate timing, and a cross-sectional image can be extracted with less invasiveness.

Abstract

L'invention porte sur un dispositif de diagnostic sur image tomographique à cohérence optique grâce auquel on peut réduire la charge de travail d'un utilisateur et les causes d'une dégradation de la qualité d'image et d'un diagnostic erroné sur une image tomographique peuvent être éliminées. L'invention porte spécifiquement sur un dispositif de diagnostic d'image acquérant une lumière réfléchie par un vaisseau sanguin à partir d'une unité d'émission/réception par connexion d'une sonde optique à celui-ci et balayage radial par l'unité d'émission/réception, et générant une pluralité d'images tomographiques du vaisseau sanguin sur la base de la lumière réfléchie acquise, le dispositif de diagnostic d'image comportant un panneau d'utilisation (112) destiné à désigner une région d'intérêt dans une image en coupe transversale générée sur la base de la lumière réfléchie acquise par l'unité d'émission/réception tandis qu'on arrête le travelling arrière et qu'on exécute un balayage rotatif dans le vaisseau sanguin, et une unité de détermination du début de l'utilisation (405) pour le calcul de la valeur d'évaluation pour déterminer l'absence ou la présence de sang dans le vaisseau sanguin, à l'aide de données d'image sur l'image en coupe transversale correspondant à la région d'intérêt désignée, et à donner une instruction du démarrage de la mémorisation de l'image en coupe transversale lorsque la valeur d'évaluation calculée satisfait à une condition prédéterminée.
PCT/JP2010/000525 2009-02-19 2010-01-29 Dispositif de diagnostic sur image et son procédé de commande WO2010095370A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP2011500483A JP5628785B2 (ja) 2009-02-19 2010-01-29 画像診断装置

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2009037040 2009-02-19
JP2009-037040 2009-02-19

Publications (1)

Publication Number Publication Date
WO2010095370A1 true WO2010095370A1 (fr) 2010-08-26

Family

ID=42633661

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2010/000525 WO2010095370A1 (fr) 2009-02-19 2010-01-29 Dispositif de diagnostic sur image et son procédé de commande

Country Status (2)

Country Link
JP (1) JP5628785B2 (fr)
WO (1) WO2010095370A1 (fr)

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2014526283A (ja) * 2011-08-31 2014-10-06 ヴォルカノ コーポレイション 血管内のイメージング及びフラッシングのための方法
US10631718B2 (en) 2015-08-31 2020-04-28 Gentuity, Llc Imaging system includes imaging probe and delivery devices
US10898140B2 (en) 2014-09-26 2021-01-26 Terumo Kabushiki Kaisha Tomographic image forming apparatus and control method
JP2022031226A (ja) * 2020-08-06 2022-02-18 キヤノン ユーエスエイ，インコーポレイテッド 自動プルバックトリガの方法及びシステム
US11278206B2 (en) 2015-04-16 2022-03-22 Gentuity, Llc Micro-optic probes for neurology
US11684242B2 (en) 2017-11-28 2023-06-27 Gentuity, Llc Imaging system

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH07194588A (ja) * 1993-11-26 1995-08-01 Toshiba Medical Eng Co Ltd Ｘ線コンピュータ断層撮影装置
JP2003028791A (ja) * 2001-05-09 2003-01-29 Olympus Optical Co Ltd 光イメージング装置
JP2005237827A (ja) * 2004-02-27 2005-09-08 Terumo Corp 治療用カテーテルおよび治療装置
JP2008510586A (ja) * 2004-08-24 2008-04-10 ザ ジェネラル ホスピタル コーポレイション 血管セグメントを画像化する方法および装置
JP2009011863A (ja) * 2001-12-20 2009-01-22 Toshiba Corp Ｘ線コンピュータ断層撮影装置

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH0824665B2 (ja) * 1986-11-28 1996-03-13 オリンパス光学工業株式会社 内視鏡装置
JP2006198225A (ja) * 2005-01-21 2006-08-03 Hitachi Medical Corp 磁気共鳴イメージング装置
US7860555B2 (en) * 2005-02-02 2010-12-28 Voyage Medical, Inc. Tissue visualization and manipulation system
DE102005032961A1 (de) * 2005-07-14 2007-01-18 Siemens Ag Verfahren und Vorrichtung zur Erzeugung eines Bildes mittels optischer Kohärenztomographie

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH07194588A (ja) * 1993-11-26 1995-08-01 Toshiba Medical Eng Co Ltd Ｘ線コンピュータ断層撮影装置
JP2003028791A (ja) * 2001-05-09 2003-01-29 Olympus Optical Co Ltd 光イメージング装置
JP2009011863A (ja) * 2001-12-20 2009-01-22 Toshiba Corp Ｘ線コンピュータ断層撮影装置
JP2005237827A (ja) * 2004-02-27 2005-09-08 Terumo Corp 治療用カテーテルおよび治療装置
JP2008510586A (ja) * 2004-08-24 2008-04-10 ザ ジェネラル ホスピタル コーポレイション 血管セグメントを画像化する方法および装置

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2014526283A (ja) * 2011-08-31 2014-10-06 ヴォルカノ コーポレイション 血管内のイメージング及びフラッシングのための方法
US10898140B2 (en) 2014-09-26 2021-01-26 Terumo Kabushiki Kaisha Tomographic image forming apparatus and control method
US11278206B2 (en) 2015-04-16 2022-03-22 Gentuity, Llc Micro-optic probes for neurology
US10631718B2 (en) 2015-08-31 2020-04-28 Gentuity, Llc Imaging system includes imaging probe and delivery devices
US11064873B2 (en) 2015-08-31 2021-07-20 Gentuity, Llc Imaging system includes imaging probe and delivery devices
US11583172B2 (en) 2015-08-31 2023-02-21 Gentuity, Llc Imaging system includes imaging probe and delivery devices
US11937786B2 (en) 2015-08-31 2024-03-26 Gentuity, Llc Imaging system includes imaging probe and delivery devices
US11684242B2 (en) 2017-11-28 2023-06-27 Gentuity, Llc Imaging system
JP2022031226A (ja) * 2020-08-06 2022-02-18 キヤノン ユーエスエイ，インコーポレイテッド 自動プルバックトリガの方法及びシステム
US11944778B2 (en) 2020-08-06 2024-04-02 Canon U.S.A., Inc. Methods and systems for automatic pullback trigger

Also Published As

Publication number Publication date
JP5628785B2 (ja) 2014-11-19
JPWO2010095370A1 (ja) 2012-08-23

Similar Documents

Publication Publication Date Title
US9295450B2 (en) Imaging apparatus and control method thereof
JP4768494B2 (ja) 画像診断装置およびその処理方法
JP5485760B2 (ja) 光干渉断層像形成装置及びその制御方法
US7905838B2 (en) Image diagnostic system and apparatus, and processing method therefor
JP5002429B2 (ja) 光干渉断層画像診断装置
JP5592137B2 (ja) 光画像診断装置及びその表示制御方法
JP5981557B2 (ja) 画像診断装置
WO2011039983A1 (fr) Appareil d'imagerie diagnostique et procédé pour le commander
JP6059334B2 (ja) 画像診断装置及び情報処理装置及びそれらの作動方法、プログラム及びコンピュータ可読記憶媒体
JP5628785B2 (ja) 画像診断装置
JP2012200532A (ja) 画像診断装置及び表示方法
JP5524947B2 (ja) 画像診断装置及びその作動方法
JP5718819B2 (ja) 画像診断装置及びその制御方法
JPWO2016047773A1 (ja) 断層像形成装置および制御方法
JP5508092B2 (ja) 光画像診断装置及びその表示制御方法
JP5399844B2 (ja) 画像診断装置及びその作動方法
WO2014049641A1 (fr) Dispositif d'imagerie diagnostique, dispositif de traitement de l'information, et procédé de commande de dispositif d'imagerie diagnostique et de dispositif de traitement de l'information
JP6809905B2 (ja) 画像診断装置、画像診断装置の作動方法及びプログラム

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 10743502

Country of ref document: EP

Kind code of ref document: A1

ENP Entry into the national phase

Ref document number: 2011500483

Country of ref document: JP

Kind code of ref document: A

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 10743502

Country of ref document: EP

Kind code of ref document: A1