WO2014049634A1 - Diagnostic imaging device, information processing device, and method for controlling diagnostic imaging device and information processing device - Google Patents

Diagnostic imaging device, information processing device, and method for controlling diagnostic imaging device and information processing device Download PDF

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Publication number
WO2014049634A1
WO2014049634A1 PCT/JP2012/006090 JP2012006090W WO2014049634A1 WO 2014049634 A1 WO2014049634 A1 WO 2014049634A1 JP 2012006090 W JP2012006090 W JP 2012006090W WO 2014049634 A1 WO2014049634 A1 WO 2014049634A1
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sectional image
cross
ultrasonic
image
optical
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PCT/JP2012/006090
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French (fr)
Japanese (ja)
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賢二 金子
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テルモ株式会社
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Priority to PCT/JP2012/006090 priority Critical patent/WO2014049634A1/en
Publication of WO2014049634A1 publication Critical patent/WO2014049634A1/en

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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/04Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor combined with photographic or television appliances
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/12Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/13Tomography
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4416Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to combined acquisition of different diagnostic modalities, e.g. combination of ultrasound and X-ray acquisitions
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4444Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
    • A61B8/445Details of catheter construction
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/46Ultrasonic, sonic or infrasonic diagnostic devices with special arrangements for interfacing with the operator or the patient
    • A61B8/461Displaying means of special interest
    • A61B8/463Displaying means of special interest characterised by displaying multiple images or images and diagnostic data on one display
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5215Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A61B8/5238Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image
    • A61B8/5261Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for combining image data of patient, e.g. merging several images from different acquisition modes into one image combining images from different diagnostic modalities, e.g. ultrasound and X-ray

Abstract

The present invention enables the diagnosis of biological tissue to be performed with high precision, while suppressing the visual loss of information possessed by an ultrasound cross-sectional image and an optical cross-sectional image of the same location in the biological tissue, when the ultrasound cross-sectional image and optical cross-sectional image are displayed. Thus, this diagnostic imaging device is configured so as to initially display an optical coherence tomography (OCT) cross-sectional image (i.e., an optical cross-sectional image). The diagnostic imaging device is further configured in such a manner as to display an intravascular ultrasound (IVUS) cross-sectional image once the OCT cross-sectional image has been displayed over C_oct × ΔT time. The IVUS cross-sectional image is displayed over C_ivus × ΔT time. This process is subsequently repeated.

Description

Image diagnostic apparatus, information processing apparatus, and control method thereof

The present invention relates to a technique for displaying a tomographic image of a biological tissue using ultrasound and light.

Conventionally, diagnostic imaging devices have been widely used for diagnosis of arteriosclerosis, preoperative diagnosis at the time of endovascular treatment with a high-function catheter such as a balloon catheter or a stent, or confirmation of postoperative results.

The diagnostic imaging apparatus includes an intravascular ultrasonic diagnostic apparatus (IVUS: IntraVascular Ultra Sound), an optical coherence tomographic diagnostic apparatus (OCT: Optical Coherence Tomography), and the like, each having different characteristics.

Recently, an image diagnostic apparatus combining an IVUS function and an OCT function (an image diagnostic apparatus including an ultrasonic transmission / reception unit capable of transmitting / receiving ultrasonic waves and an optical transmission / reception unit capable of transmitting / receiving light) has also been proposed. (For example, see Patent Documents 1 and 2). According to such an image diagnostic apparatus, both a cross-sectional image utilizing the characteristics of IVUS that can be measured up to a high depth region and a cross-sectional image utilizing the characteristics of OCT that can be measured with high resolution are generated by a single scan. be able to.

JP-A-11-56752 JP 2006-204430 A

As described above, it is possible to generate a cross-sectional image of the same location in the blood vessel by both the IVUS function and the OCT function. Although an OCT cross-sectional image is a high-resolution image for a relatively shallow tissue, there is a problem that an image of a deeper tissue cannot be obtained. On the other hand, the IVUS cross-sectional image is convenient for obtaining an image including a relatively deep living tissue, but has a surface that is not as high as OCT. That is, it can be said that these two types of cross-sectional images are complementary to each other.

The display so far has been either displaying these two types of cross-sectional images side by side, or combining the two types of cross-sectional images to generate a single composite image and displaying it.

In the former case, the user needs to compare two types of cross-sectional images separated from each other on the screen, and the situation of the affected area can only be imagined in the user's own head.

On the other hand, in the latter case, the burden on the user's diagnosis is reduced as much as it is not necessary to move the viewpoint. However, a general method in the case of synthesizing two cross-sectional images is to calculate an average value of pixel values of the two cross-sectional images and use the average value as a value of one pixel of the synthesized image. Therefore, for example, the characteristic of the OCT cross-sectional image in the composite image is half of the characteristic of the original OCT cross-sectional image, which means that half of the information of the original OCT cross-sectional image is lost. This is also true for IVUS cross-sectional images.

Also, there are some that display relatively shallow tissues with OCT that can be measured with high resolution, and relatively deep tissues with IVUS that can measure up to a deep region. Also in this case, information on the IVUS tomographic image obtained by measuring the relatively shallow tissue and the OCT tomographic image obtained by measuring the relatively deep tissue are lost.

The present invention has been made in view of such problems, and at the time of displaying an ultrasonic cross-sectional image and an optical cross-sectional image of the same location in a living tissue, while suppressing visual loss of information held by each, with high accuracy. It is intended to provide a technique capable of diagnosing a living tissue.

In order to achieve the above object, the diagnostic imaging apparatus according to the present invention has the following configuration. That is,
From a living tissue received by the ultrasonic transmission / reception unit, holding a probe having a transmission / reception unit in which an ultrasonic transmission / reception unit for transmitting / receiving ultrasonic waves and an optical transmission / reception unit for transmitting / receiving light are arranged rotatably and detachably. An ultrasonic diagnostic image and an optical cross-sectional image of the biological tissue using the reflected wave and the reflected light from the biological tissue received by the optical transceiver,
Storage means for storing the generated ultrasonic cross-sectional image and the optical cross-sectional image;
Display control means for alternately displaying the ultrasonic cross-sectional image and the optical cross-sectional image stored in the storage means in one image display area along the time axis.

Another invention has the following configuration. That is,
An information processing apparatus that displays the ultrasonic cross-sectional image and the optical cross-sectional image obtained by an image diagnostic apparatus that generates an ultrasonic cross-sectional image and an optical cross-sectional image,
Access means for accessing a storage medium for storing the ultrasonic cross-sectional image and the optical cross-sectional image;
Display control means for alternately displaying the ultrasonic cross-sectional image and the optical cross-sectional image read by the access means in one image display area along the time axis.

According to the present invention, when displaying an ultrasonic cross-sectional image and an optical cross-sectional image at the same location in a living tissue, it is possible to diagnose a living tissue with high accuracy while suppressing visual loss of information held by each. become.

The accompanying drawings are included in the specification, constitute a part thereof, show an embodiment of the present invention, and are used to explain the principle of the present invention together with the description.
1 is a diagram illustrating an external configuration of a diagnostic imaging apparatus 100 according to an embodiment of the present invention. It is a figure which shows the whole structure of a probe part, and the cross-sectional structure of a front-end | tip part. It is a figure which shows the cross-sectional structure of an imaging core, and arrangement | positioning of an ultrasonic transmission / reception part and an optical transmission / reception part. 2 is a diagram illustrating a functional configuration of the diagnostic imaging apparatus 100. FIG. It is a figure which shows the example of the user interface in parallel display mode. It is a figure which shows the example of the user interface in alternate display mode. It is a figure which shows the example of the user interface in alternate display mode. It is a figure which shows the example of the IVUS image and OCT image which are constructed | assembled in memory when the intravascular scan is completed. It is a flowchart which shows the process sequence of the signal processing part in the alternate display mode in embodiment. 10 is a flowchart showing details of a display freeze process in FIG. 9. FIG. 10 is a flowchart showing an alternate display parameter changing process in FIG. 9. FIG.

Hereinafter, embodiments according to the present invention will be described in detail with reference to the accompanying drawings.

1. External Configuration Figure 1 of an image diagnostic apparatus is a diagram illustrating an exemplary diagnostic imaging apparatus according to Embodiment 100 external configuration of (a function of the IVUS, image diagnostic apparatus and a function of OCT) of the present invention.

As shown in FIG. 1, the diagnostic imaging apparatus 100 includes a probe unit 101, a scanner and pullback unit 102, and an operation control device 103, and the scanner and pullback unit 102 and the operation control device 103 are connected by a signal line 104. Various signals are connected so that transmission is possible.

The probe unit 101 is directly inserted into a blood vessel, transmits an ultrasonic wave based on a pulse signal into the blood vessel, and receives an reflected wave from the blood vessel, and transmitted light (measurement light). An imaging core including an optical transmission / reception unit that continuously transmits the light into the blood vessel and continuously receives the reflected light from the blood vessel is inserted. In the diagnostic imaging apparatus 100, the state inside the blood vessel is measured by using the imaging core.

The scanner and pullback unit 102 is detachably attached to the probe unit 101, and operates in the axial direction and rotational direction in the blood vessel of the imaging core inserted in the probe unit 101 by driving a built-in motor. It prescribes. Further, the reflected wave received by the ultrasonic transmission / reception unit and the reflected light received by the optical transmission / reception unit are acquired and transmitted to the operation control apparatus 103.

The operation control device 103 performs a function of inputting various setting values and processes data obtained by the measurement, and displays a cross-sectional image (lateral cross-sectional image and vertical cross-sectional image) in the blood vessel. It has the function to do.

The transverse cross-sectional image here is a cross-sectional image of a blood vessel cut substantially perpendicular to the longitudinal axis direction of the blood vessel, and the vertical cross-sectional image is substantially parallel to the longitudinal axis direction of the blood vessel. This refers to a cross-sectional image of a blood vessel cut.

In the operation control device 103, 111 is a main body control unit, which generates ultrasonic data based on the reflected wave obtained by measurement, and processes the line data generated based on the ultrasonic data, An ultrasonic cross-sectional image is generated. Further, interference light data is generated by causing interference between the reflected light obtained by measurement and the reference light obtained by separating the light from the light source, and line data generated based on the interference light data. To generate an optical cross-sectional image.

111-1 is a printer and a DVD recorder, which prints the processing results in the main body control unit 111 or stores them as data. Reference numeral 112 denotes an operation panel, and the user inputs various setting values and instructions via the operation panel 112. Reference numeral 113 denotes an LCD monitor as a display device, which displays a cross-sectional image generated by the main body control unit 111.

2. Sectional configuration of the entire configuration and the tip of the probe portion will be described with reference to FIG sectional configuration of the entire configuration and the tip of the probe portion 101. As shown in FIG. 2, the probe unit 101 includes a long catheter sheath 201 that is inserted into a blood vessel, and a connector that is disposed on the user's hand side without being inserted into the blood vessel to be operated by the user. Part 202. A guide wire lumen tube 203 constituting a guide wire lumen is provided at the distal end of the catheter sheath 201. The catheter sheath 201 forms a continuous lumen from a connection portion with the guide wire lumen tube 203 to a connection portion with the connector portion 202.

Inside the lumen of the catheter sheath 201 is provided with a transmission / reception unit 221 in which an ultrasonic transmission / reception unit for transmitting / receiving ultrasonic waves and an optical transmission / reception unit for transmitting / receiving light, an electric signal cable and an optical fiber cable are provided. An imaging core 220 including a coil-shaped drive shaft 222 that transmits a rotational drive force for rotating the catheter sheath 201 is inserted over almost the entire length of the catheter sheath 201.

The connector portion 202 includes a sheath connector 202a configured integrally with the proximal end of the catheter sheath 201, and a drive shaft connector 202b configured by rotatably fixing the drive shaft 222 to the proximal end of the drive shaft 222. Prepare.

A kink protector 211 is provided at the boundary between the sheath connector 202a and the catheter sheath 201. Thereby, predetermined rigidity is maintained, and bending (kink) due to a sudden change in physical properties can be prevented.

The base end of the drive shaft connector 202b is detachably attached to the scanner and the pullback unit 102.

Next, the cross-sectional configuration of the tip portion of the probe unit 101 will be described. Inside the lumen of the catheter sheath 201 is a housing 223 in which an ultrasonic transmission / reception unit for transmitting / receiving ultrasonic waves and an optical transmission / reception unit for transmitting / receiving light are arranged, and a rotation for rotating the housing 223 An imaging core 220 including a driving shaft 222 that transmits a driving force is inserted through substantially the entire length to form the probe unit 101.

The drive shaft 222 is capable of rotating and axially moving the transmission / reception unit 221 with respect to the catheter sheath 201. The drive shaft 222 is made of a metal wire such as stainless steel that is flexible and can transmit rotation well. It is composed of multiple multilayer close-contact coils and the like. An electric signal cable and an optical fiber cable (single mode optical fiber cable) are arranged inside.

The housing 223 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, MIM (metal powder injection molding) or the like. Further, a short coil-shaped elastic member 231 is provided on the tip side.

The elastic member 231 is a stainless steel wire formed in a coil shape, and the elastic member 231 is disposed on the distal end side, thereby preventing the imaging core 220 from being caught in the catheter sheath 201 when moving the imaging core 220 back and forth.

232 is a reinforcing coil, which is provided for the purpose of preventing a sharp bending of the distal end portion of the catheter sheath 201.

The guide wire lumen tube 203 has a guide wire lumen into which a guide wire can be inserted. The guide wire lumen tube 203 is used to receive a guide wire previously inserted into a blood vessel and guide the catheter sheath 201 to the affected area with the guide wire.

3. Next, the cross-sectional configuration of the imaging core 220 and the arrangement of the ultrasonic transmission / reception unit and the optical transmission / reception unit will be described. FIG. 3 is a diagram illustrating a cross-sectional configuration of the imaging core and an arrangement of the ultrasonic transmission / reception unit and the optical transmission / reception unit.

As shown to 3A of FIG. 3, the transmission / reception part 221 arrange | positioned in the housing 223 is provided with the ultrasonic transmission / reception part 310 and the optical transmission / reception part 320, and each of the ultrasonic transmission / reception part 310 and the optical transmission / reception part 320 is a drive. It is arranged along the axial direction on the rotation center axis of the shaft 222 (on the one-dot chain line of 3A).

Among these, the ultrasonic transmission / reception unit 310 is disposed on the distal end side of the probe unit 101, and the optical transmission / reception unit 320 is disposed on the proximal end side of the probe unit 101.

Further, the ultrasonic transmission / reception unit 310 and the optical transmission / reception unit 320 include an ultrasonic transmission direction (elevation angle direction) of the ultrasonic transmission / reception unit 310 and an optical transmission direction (elevation angle direction) of the optical transmission / reception unit 320 with respect to the axial direction of the drive shaft 222. ) Are mounted in the housing 223 so as to be approximately 90 °. In addition, it is desirable that each transmission direction is attached with a slight shift from 90 ° so as not to receive reflection on the inner surface of the lumen of the catheter sheath 201.

Inside the drive shaft 222, an electric signal cable 311 connected to the ultrasonic transmission / reception unit 310 and an optical fiber cable 321 connected to the optical transmission / reception unit 320 are arranged, and the electric signal cable 311 is an optical fiber. The cable 321 is spirally wound.

3B in FIG. 3 is a cross-sectional view of the ultrasonic wave transmission / reception position cut along a plane substantially orthogonal to the rotation center axis. As shown in 3B of FIG. 3, when the downward direction on the paper is 0 degree, the ultrasonic transmission direction (rotational angle direction (also referred to as azimuth angle direction)) of the ultrasonic transmission / reception unit 310 is θ degrees.

3C in FIG. 3 is a cross-sectional view of the optical transmission / reception position taken along a plane substantially orthogonal to the rotation center axis. As shown in 3C of FIG. 3, when the downward direction on the paper is 0 degree, the light transmission direction (rotation angle direction) of the light transmitting / receiving unit 320 is 0 degree. That is, in the ultrasonic transmission / reception unit 310 and the optical transmission / reception unit 320, the ultrasonic transmission direction (rotation angle direction) of the ultrasonic transmission / reception unit 310 and the optical transmission direction (rotation angle direction) of the optical transmission / reception unit 320 are mutually θ degrees. It is arranged so as to be displaced.

4). Functional configuration of diagnostic imaging apparatus Next, a functional configuration of the diagnostic imaging apparatus 100 will be described. FIG. 4 is a diagram illustrating a functional configuration of the diagnostic imaging apparatus 100 that combines the function of IVUS and the function of OCT (here, a wavelength sweep type OCT). Note that the diagnostic imaging apparatus combining the IVUS function and the other OCT functions also has the same functional configuration, and thus the description thereof is omitted here.

(1) Function of IVUS The imaging core 220 includes an ultrasonic transmission / reception unit 310 inside the tip, and the ultrasonic transmission / reception unit 310 transmits ultrasonic waves based on the pulse wave transmitted from the ultrasonic signal transmitter / receiver 452. While transmitting to a biological tissue, the reflected wave (echo) is received, and it transmits to the ultrasonic signal transmitter / receiver 452 as an ultrasonic signal via the adapter 402 and the slip ring 451.

In the scanner and pullback unit 102, the rotational drive unit side of the slip ring 451 is rotationally driven by a radial scanning motor 405 of the rotational drive unit 404. Further, the rotation angle of the radial scanning motor 405 is detected by the encoder unit 406. Further, the scanner and pullback unit 102 includes a linear drive device 407 and defines the axial operation of the imaging core 220 based on a signal from the signal processing unit 428.

The ultrasonic signal transmitter / receiver 452 includes a transmission wave circuit and a reception wave circuit (not shown). The transmission wave circuit transmits a pulse wave to the ultrasonic transmission / reception unit 310 in the imaging core 220 based on the control signal transmitted from the signal processing unit 428.

Further, the reception wave circuit receives an ultrasonic signal from the ultrasonic transmission / reception unit 310 in the imaging core 220. The received ultrasonic signal is amplified by the amplifier 453 and then input to the detector 454 for detection.

Further, the A / D converter 455 samples the ultrasonic signal output from the detector 454 for 200 points at 30.6 MHz to generate one line of digital data (ultrasound data). Here, 30.6 MHz is assumed, but this is calculated on the assumption that 200 points are sampled at a depth of 5 mm when the sound speed is 1530 m / sec. Therefore, the sampling frequency is not particularly limited to this.

The line-unit ultrasonic data generated by the A / D converter 455 is input to the signal processing unit 428. The signal processing unit 428 generates ultrasonic cross-sectional images at each position in the blood vessel by converting the ultrasonic data to gray scale, and outputs the ultrasonic cross-sectional image to the LCD monitor 113 at a predetermined frame rate.

Note that the signal processing unit 428 is connected to the motor control circuit 429 and receives the video synchronization signal of the motor control circuit 429. The signal processing unit 428 generates an ultrasonic cross-sectional image in synchronization with the received video synchronization signal.

The video synchronization signal of the motor control circuit 429 is also sent to the rotation drive device 404, and the rotation drive device 404 outputs a drive signal synchronized with the video synchronization signal.

Note that the signal processing unit 428 and the image processing related to the user interface in the diagnostic imaging apparatus 100 described later with reference to FIG. 6 to FIG. It shall be realized in

(2) Function of wavelength sweep type OCT Next, the functional configuration of the wavelength sweep type OCT will be described with reference to FIG. Reference numeral 408 denotes a wavelength swept light source (Swept Laser), which is a type of Extended-cavity Laser composed of an optical fiber 416 and a polygon scanning filter (408b) coupled in a ring shape with an SOA 415 (semiconductor optical amplifier).

The light output from the SOA 415 travels through the optical fiber 416 and enters the polygon scanning filter 408b. The light whose wavelength is selected here is amplified by the SOA 415 and finally output from the coupler 414.

In the polygon scanning filter 408b, the wavelength is selected by a combination of the diffraction grating 412 for separating light and the polygon mirror 409. Specifically, the light split by the diffraction grating 412 is condensed on the surface of the polygon mirror 409 by two lenses (410, 411). As a result, only light having a wavelength orthogonal to the polygon mirror 409 returns through the same optical path and is output from the polygon scanning filter 408b. That is, the wavelength time sweep can be performed by rotating the polygon mirror 409.

As the polygon mirror 409, for example, a 48-sided mirror is used, and the rotation speed is about 50000 rpm. The wavelength sweeping method combining the polygon mirror 409 and the diffraction grating 412 enables high-speed, high-output wavelength sweeping.

The light of the wavelength swept light source 408 output from the Coupler 414 is incident on one end of the first single mode fiber 440 and transmitted to the distal end side. The first single mode fiber 440 is optically coupled to the second single mode fiber 445 and the third single mode fiber 444 at an intermediate optical coupler 441.

An optical rotary joint (optical cup) that transmits light by coupling a non-rotating part (fixed part) and a rotating part (rotational drive part) to the tip side of the optical coupler part 441 of the first single mode fiber 440. A ring portion) 403 is provided in the rotary drive device 404.

Further, the fifth single mode fiber 443 of the probe unit 101 is detachably connected to the distal end side of the fourth single mode fiber 442 in the optical rotary joint (optical coupling unit) 403 via the adapter 402. Yes. As a result, the light from the wavelength swept light source 408 is transmitted to the fifth single mode fiber 443 that is inserted into the imaging core 220 and can be driven to rotate.

The transmitted light is irradiated from the optical transceiver 320 of the imaging core 220 to the living tissue in the blood vessel while rotating and moving in the axial direction. Then, a part of the reflected light scattered on the surface or inside of the living tissue is taken in by the optical transmission / reception unit 320 of the imaging core 220, and returns to the first single mode fiber 440 side through the reverse optical path. Further, a part of the optical coupler unit 441 moves to the second single mode fiber 445 side, and is emitted from one end of the second single mode fiber 445, and then received by a photodetector (eg, a photodiode 424). The

Note that the rotation drive unit side of the optical rotary joint 403 is rotationally driven by a radial scanning motor 405 of the rotation drive unit 404.

On the other hand, an optical path length variable mechanism 432 for finely adjusting the optical path length of the reference light is provided at the tip of the third single mode fiber 444 opposite to the optical coupler section 441.

The optical path length variable mechanism 432 changes the optical path length to change the optical path length corresponding to the variation in length so that the variation in length of each probe unit 101 when the probe unit 101 is replaced and used can be absorbed. Means.

The third single mode fiber 444 and the collimating lens 418 are provided on a uniaxial stage 422 that is movable in the direction of the optical axis as indicated by an arrow 423, and form optical path length changing means.

Specifically, when the probe unit 101 is replaced, the uniaxial stage 422 functions as an optical path length changing unit having a variable range of the optical path length that can absorb variations in the optical path length of the probe unit 101. Further, the uniaxial stage 422 also has a function as an adjusting means for adjusting the offset. For example, even when the tip of the 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 so as to interfere with the reflected light from the surface position of the living tissue. Is possible.

The optical path length is finely adjusted by the uniaxial stage 422, and the light reflected by the mirror 421 via the grating 419 and the lens 420 is first coupled by the optical coupler unit 441 provided in the middle of the third single mode fiber 444. It is mixed with the light obtained from the single mode fiber 440 side and received by the photodiode 424.

The interference light received by the photodiode 424 in this way is photoelectrically converted, amplified by the amplifier 425, and then input to the demodulator 426. The demodulator 426 performs demodulation processing for extracting only the signal portion of the interfered light, and its output is input to the A / D converter 427 as an interference light signal.

The A / D converter 427 samples the interference light signal for 2048 points at 90 MHz, for example, and generates one line of digital data (interference light data). The sampling frequency of 90 MHz is based on the premise that about 90% of the wavelength sweep cycle (25.0 μsec) is extracted as 2048 digital data when the wavelength sweep repetition frequency is 40 kHz. However, the present invention is not limited to this.

The line-by-line interference light data generated by the A / D converter 427 is input to the signal processing unit 428. In the signal processing unit 428, the interference light data is frequency-resolved by FFT (Fast Fourier Transform) to generate data in the depth direction (line data), and this is coordinate-converted to obtain an optical cross section at each position in the blood vessel. An image is constructed and output to the LCD monitor 113 at a predetermined frame rate.

The signal processing unit 428 is further connected to the optical path length adjusting means control device 430. The signal processing unit 428 controls the position of the uniaxial stage 422 via the optical path length adjusting unit controller 430.

Note that these processes in the signal processing unit 428 are also realized by executing a predetermined program by a computer.

In the above configuration, when the user operates the operation control device 103 and inputs a scan start instruction, the signal processing unit 428 controls the scanner and the pullback unit 102 to rotate the imaging core 220 and set the image core 220 to a predetermined value. Pulling at a speed causes the blood vessel to move in the longitudinal direction. As a result, as described above, since the A / D converters 427 and 455 output digital ultrasonic data and interference light data, the signal processing unit 428 moves in the moving direction of the imaging core 220 in them. An ultrasonic cross-sectional image and an optical cross-sectional image at each position along the path are constructed in the memory 428 a included in the signal processing unit 428. At this time, the scales of the ultrasonic cross-sectional image and the optical cross-sectional image are made to coincide with each other, and the center position of each cross-sectional image is made to coincide with the rotation axis at the time of scanning. FIG. 8 shows an example of an ultrasonic cross-sectional image and an optical cross-sectional image stored in the memory 428 a included in the signal processing unit 428. As described above, the emission directions of the ultrasonic transmission / reception unit 310 and the optical transmission / reception unit 320 are shifted by θ as shown in 3B of FIG. The orientations of these two types of cross-sectional images are combined together by shifting them. Further, as shown in 3A of FIG. 3, the ultrasonic transmission / reception unit 310 and the optical transmission / reception unit 320 are shifted by L with respect to the moving direction of the imaging core 220 by the pull-back operation. In order to obtain an image and an optical cross-sectional image, it is assumed that the reconstructed cross-sectional image is also shifted by L as shown in FIG. 8, for example, to obtain an ultrasonic cross-sectional image at the same position as a certain optical cross-sectional image. Is acquired from a position shifted by L.

Note that the above θ and L may be set by operating the operation control device 103 at the start of scanning.

5. Description of User Interface Next, a user interface displayed on the LCD monitor 113 will be described. The following description will be made on the assumption that the scanning of the patient's blood vessel has already been completed and the cross-sectional image generation processing at each position as shown in FIG. 8 has been completed.

The cross-sectional image display in the embodiment includes an alternate display mode in addition to a normal mode (parallel display mode) in which an ultrasonic cross-sectional image and an optical cross-sectional image are displayed in parallel. Therefore, the normal parallel display mode will be described first, and then the alternate display mode will be described.

FIG. 5 is a diagram showing an example of the user interface 500 in the parallel display mode displayed on the LCD monitor 113. By clicking the “Parallel display” button 501 at the upper right of the screen shown in the drawing with a cursor linked to a pointing device such as a mouse, the “Parallel display” user interface is displayed.

As shown in FIG. 5, the user interface in this mode includes a horizontal cross-sectional image display area 510 for displaying a horizontal cross-sectional image generated by the signal processing unit 428 and a vertical cross-sectional image display for displaying a vertical cross-sectional image. An area 520 and an operation area 530 in which buttons for designating the parallel display mode and the alternate display mode are arranged.

The lateral cross-sectional image display area 510 further includes an OCT cross-sectional image display area 511 for displaying an OCT cross-sectional image (optical cross-sectional image) generated using the OCT function, and an IVUS cross-sectional image generated using the IVUS function ( IVUS cross-sectional image display area 512 for displaying an ultrasonic cross-sectional image).

The vertical cross-sectional image display area 520 displays a vertical cross-sectional image 521 generated based on a plurality of IVUS cross-sectional images. The arrow-shaped pointer 522 displayed in the vertical cross-sectional image display area 520 designates a predetermined position in the axial direction of the vertical cross-sectional image 521, and the position can be freely changed with a mouse or the like. It has become. In the above-described OCT cross-sectional image display area 511 and IVUS cross-sectional image display area 512, the OCT cross-sectional image and the IVUS cross-sectional image at the position specified by the pointer 522 are displayed.

Therefore, when examining the inside of a patient's blood vessel, the mouse is operated, the pointer 522 is freely moved, and the IVUS cross-sectional image and the OCT cross-sectional image displayed each time are viewed to diagnose the patient's blood vessel. be able to.

The above is the description of the user interface in the parallel display mode. Next, a user interface in the alternate display mode in the embodiment will be described with reference to FIGS.

In the parallel display mode of FIG. 5 described above, the OCT cross-sectional image and the IVUS cross-sectional image are compared to diagnose the state of the patient's blood vessel. An OCT cross-sectional image can provide a high-resolution image of the relatively shallow tissue, but is not suitable for obtaining a deep tissue image. On the other hand, the IVUS cross-sectional image can obtain a relatively deep tissue image although the resolution is inferior to that of the OCT cross-sectional image. That is, it can be said that the OCT cross-sectional image and the IVUS cross-sectional image have a complementary relationship. Therefore, it is advantageous for diagnosis if these two images can be confirmed at the same time without changing the viewpoint. For that purpose, it is conceivable to combine these two images, generate one composite image, and display it. However, if two images are combined and displayed at a ratio of 50:50, the contrast of the original individual images is half that of the original images, which hinders diagnosis. End up. Therefore, in the present embodiment, the OCT cross-sectional image and the IVUS cross-sectional image are not combined and displayed as one image, but these two types of images are alternately displayed along the time axis. This display mode is the “alternate display mode” referred to in the embodiment. This alternate display mode is shifted to by clicking the “alternate display” button 502 in the operation area 530 in FIG.

6 and 7 respectively show the instantaneous display state of the user interface 500 in the alternate display mode in the embodiment. The difference between FIG. 6 and FIG. 7 is an indicator that indicates the type of cross-sectional image to be displayed and whether the displayed cross-sectional image is an OCT cross-sectional image or an IVUS cross-sectional image, and the others are the same. Therefore, hereinafter, components constituting the user interface 500 will be described with reference to the user interface 500 of FIG. Also, the longitudinal section image display area 520 and the operation area 530 in FIG. 6 are the same as those in FIG.

6, only one of the areas 651 for displaying the cross-sectional image is displayed in the horizontal cross-sectional image display area 530 in the user interface 500. In this region 651, the OCT cross-sectional image and the IVUS cross-sectional image are alternately displayed along the time axis, and hence this is referred to as an alternate display region hereinafter. Since the images are displayed alternately, in order to let the user know which image is being displayed, in the embodiment, one of the indicators indicated by reference numerals 652 and 653 in the drawing is highlighted to display the cross-sectional image being displayed. Displays which is. In the case of FIG. 6, since the indicator 652 is highlighted, it is indicated that what is displayed in the alternate display area 651 is an OCT cross-sectional image. On the other hand, in the case of FIG. 7, since the indicator 653 is highlighted, it is indicated that the alternate display area 651 is an IVUS cross-sectional image. Note that the user can input an instruction to stop highlight display of the indicators 652 and 653 from a menu (not shown). This is because some users feel that the alternate highlight display of the indicators 652 and 653 during the alternate display of the cross-sectional images is noticeable.

Furthermore, pointers 656 to 659 are provided so that the user can set the contrast and the color independently for the OCT sectional image and the IVUS sectional image. Pointers 656 and 658 arranged on the left side of the screen are used to change the contrast and color of the OCT cross-sectional image. On the other hand, pointers 657 and 659 arranged on the right side of the screen are for changing the contrast and color of the IVUS cross-sectional image. In the drawing, the OCT cross-sectional image is displayed in R (red), and the IVUS cross-sectional image is displayed in B (blue). Here, the description has been made assuming that the color designation is selected from three colors of red, blue, and green. However, any color may be designated. In that case, a color space having three vertices of red, blue, and green may be displayed, and the pointers 658 and 659 may be movable in the space.

Furthermore, in order to make it easier to gaze at one of the two types of cross-sectional images, the pointer 660 for determining the ratio can be changed by a mouse operation when alternately displaying the images. By default, the pointer 660 is positioned at the center position as shown in the drawing so that the ratio of alternately displaying the OCT cross-sectional image and the IVUS cross-sectional image has a one-to-one relationship. Then, the display frequency of the OCT cross-sectional image is increased by moving the pointer 660 to the left side toward the screen. Conversely, when the pointer 660 is moved to the right side, the display frequency of the IVUS cross-sectional image is increased. For example, when it is set to 1: 1, the OCT cross-sectional image and the IVUS cross-sectional image are displayed for the same time and switched. When “5: 1” is set, the OCT cross-sectional image is displayed five times continuously in the alternate display area 651 and then the IVUS cross-sectional image is displayed once. In other words, when the display period of one IVUS cross-sectional image is 1, the display time of one OCT cross-sectional image can be displayed over a period five times that time. In the figure, the display ratio of the OCT cross-sectional image and the IVUS cross-sectional image can be specified in the range of “5: 1” to “1: 5”, but it should be noted that these numerical values are only examples. .

Furthermore, in the embodiment, freeze buttons 654 and 655 are provided for stopping the display in the type of cross-sectional image desired by the user while the OCT cross-sectional image and the IVUS cross-sectional image are alternately displayed. The freeze button 654 is a button for stopping the display of the OCT cross-sectional image, and the freeze button 655 is a button for stopping the display of the IVUS cross-sectional image. All the buttons are kept stopped while the mouse button is pressed at the button position, and the alternate display is resumed when the mouse button is released. It should be noted that the freeze and alternate display may be switched every time a click operation is performed instead of the freeze when the mouse button is pressed, and it should be noted that the above is an example.

In the embodiment, the pointer 661 operated by the mouse is provided so that the user can freely set the number of cross-sectional images to be displayed per unit time. When the pointer 661 is moved to the upper part of the screen, the number of cross-sectional images per unit time is increased and switching is performed at high speed. Conversely, if it moves to the lower part, the number will decrease and switching speed will become slow. A column 662 is used to express the speed of the position indicated by the pointer 661 as a numerical value.

For example, as illustrated, when the position of the pointer 661 is set to the illustrated position and the display speed is “10 f / s”, the minimum display time ΔT of one cross-sectional image is 0.1 second. When the pointer 660 is positioned at the center position shown in the drawing and the mixing ratio of the OCT cross-sectional image and the IVUS cross-sectional image is 1: 1, the OCT cross-sectional image and the IVUS cross-sectional image are each set at a time interval of 0.1 second. Will be switched. In addition, when the pointer 660 is moved to the position “4: 1” at the same display speed, the IVUS cross-sectional image is set to 0. 0 after the OCT cross-sectional image is displayed for 0.4 (= 0.1 × 4) seconds. The display for 1 second is repeated.

It is also possible to enlarge and display the alternate display area 651 on the user interface after setting an arbitrary display environment.

Further, the operation method of the user interface 500 is not limited to the above, and for example, the start and stop of the image switching display may be performed by clicking a designated portion of the user interface 500 or operating the operation panel 112.

The user interface 500 in the alternate display mode in the embodiment has been described above.

[Description of processing procedure]
The feature in this embodiment is in the alternate display mode shown in FIGS. 6 and 7 among the above two display modes. Therefore, hereinafter, the processing procedure of the signal processing unit 428 for realizing the alternate display mode will be described with reference to FIGS. 9 to 11.

Although details will become clear from the following description, the variables C_oct and C_ivus hold values determined depending on the position of the pointer 660, and C_oct defines the display time of the OCT cross-sectional image. C_ivus holds a value for defining the display time of the IVUS cross-sectional image. For example, when the pointer 660 is at a position indicating “4: 1”, C_oct = 4 and C_ivus = 1. The variable ΔT is a value determined depending on the position of the pointer 661, and holds a value indicating the minimum display time of one cross-sectional image. For example, when the pointer 661 is at a position indicating “10 f / s”, ΔT has a value of 0.1 seconds. The variable C is a variable for counting the number of cross-sectional images to be displayed continuously. Hereinafter, based on such a point, a processing procedure of the signal processing unit 428 in the alternate display mode in the embodiment will be described.

When the alternate display processing mode is started, an initial setting process is first executed in step S901. The values set here include the following.
1. The initial position of the pointer 522 is set to a preset position (for example, the position of the head OCT cross-sectional image).
2. The pointer 660 is set to “1: 1” (one to one) (the OCT cross-sectional image maximum display count C_oct is set to “1”, and the IVUS maximum display count C_ivus is set to “1”).
3. The pointer 661 is set to “10 f / s” (ΔT is set to 0.1 second).
4). Set the pointer 658 and the pointer 659 to default positions (determine the default color of the OCT slice image and the default color of the IVUS slice image).
5. Set pointers 656, 657 to default positions (determine default contrast for OCT slice images, default contrast for IVUS slice images).

Next, in step S902, an object to be displayed first is determined. In the embodiment, the first cross-sectional image to be displayed is the OCT cross-sectional image, but of course, an IVUS cross-sectional image may be used. Next, in step S903, the variable C is cleared to zero.

In step S904, it is determined whether or not there is an instruction from the user. The types of instructions include freeze buttons 654 and 655, pointers 522 and 656 to 661, a click operation on the buttons 501 and 502, and the like.

If it is determined that there is no instruction from the user, the process proceeds to step S905. In step S905, it is determined whether the current display target is an OCT cross-sectional image or an IVUS cross-sectional image. When the process proceeds to step S905 for the first time, since the OCT cross-sectional image is set as the display target in step S902, the process proceeds to step S906. In step S906, the OCT cross-sectional image is displayed in the alternate display area 651 for a period of ΔT after the set color and contrast are set. In step S907, the variable C is increased by “1”. In step S908, the value of the variable C is compared with the variable C_oct. If C <C_oct, the processes in and after S904 are repeated. As a result, the OCT cross-sectional image is displayed for a period corresponding to the set ratio. If C ≧ C_oct, the process proceeds to step S909, this time the display object is switched to the IVUS cross-sectional image, and the process returns to step S903. By returning to step S903, the IVUS cross-sectional image display count C is cleared to zero.

If it is determined in step S905 that the display target is an IVUS cross-sectional image, the process proceeds to step S910, and the IVUS cross-sectional image is set to the set color and contrast in the alternate display area 651, and then displayed for the ΔT period. To do. In step S911, the variable C is increased by “1”. In step S912, if C <C_ivus, the processes in and after step S904 are repeated. If C ≧ C_ivus, the display target is switched to the OCT cross-sectional image again in step S913, and the process returns to step S903.

As a result of the above processing, the OCT cross-sectional image and the IVUS cross-sectional image are alternately displayed in the alternate display area 651 according to the ratio indicated by the pointer 660.

If the user operates a pointer or button on the user interface during the alternate display, the process proceeds from step S904 to step S914. In step S914, it is determined whether or not the instruction input from the user is for freeze button 654 or 655. If it is determined that the instruction is input to the freeze button 654 or 655, the process proceeds to step S915 to execute display freeze processing. When the determination in step S914 is No, the instruction input from the user is any one of the pointers 656 to 661 and the buttons 501, 502, and is regarded as a parameter change instruction in the alternate display, and the process proceeds to step S916. .

Details of the display freeze process in step S915 will be described with reference to the flowchart of FIG.

First, in step S1001, it is determined whether the instruction from the user is to press the freeze button 654 (more precisely, it is determined whether the mouse button is moved to the freeze button 654 and the mouse button is pressed). ). If it is determined that the freeze button 654 has been pressed, an OCT cross-sectional image is displayed in the alternate display area 651 in step S1002 regardless of the display target at that time. In step S1003, the display of the OCT cross-sectional image is continued until it is determined that the pressing of the freeze button 654 is released. As a result, while the user presses the freeze button 654, the alternate display is temporarily stopped, and the OCT cross-sectional image continues to be displayed in the alternate display area 651.

On the other hand, if it is determined in step S1001 that the instruction from the user is not the freeze button 654, it is determined in step S1004 whether the instruction from the user is a press of the freeze button 655. If it is determined that the freeze button 655 has been pressed, an IVUS cross-sectional image is displayed in the alternate display area 651 in step S1005 regardless of the display target at that time. In step S1006, the display of the IVUS cross-sectional image is continued until it is determined that the pressing of the freeze button 655 is released. As a result, while the user presses the freeze button 655, the alternate display is temporarily stopped, and the IVUS cross-sectional image continues to be displayed in the alternate display area 651.

Next, the alternating parameter changing process in step S916 of FIG. 9 will be described with reference to the flowchart of FIG.

First, in step S1101, it is determined whether or not the instruction from the user is a movement of the pointer 522, that is, whether or not the longitudinal position of the blood vessel of the cross-sectional image to be displayed has been changed. If it is determined that the position has been changed, the process proceeds to step S1102, and based on the position of the pointer 522, an OCT cross-sectional image and an IVUS cross-sectional image to be alternately displayed are determined.

On the other hand, if it is determined that the instruction from the user is not the pointer 522, the process proceeds to step S1103, whether the position of the pointer 660 has been changed, that is, whether the display time ratio has been changed in the alternate display. Judge whether or not. If it is determined that the display time ratio is changed, the process proceeds to step S1104, and variables C_oct and C_ivus are determined according to the new ratio.

If it is determined that the instruction from the user is not the pointer 660, the process advances to step S1105 to determine whether the position of the pointer 661 has been changed, that is, whether the display speed has been changed. To do. If it is determined that the display speed is changed, the process advances to step S1106 to determine ΔT based on the position of the pointer 661 after the change.

If it is determined that the instruction from the user is not the pointer 661, the process advances to step S1107 to determine whether the position of the pointer 658 or 659 has been changed. If it is determined that any of the positions has been changed, the process proceeds to step S1108, and the color of the target cross-sectional image is changed according to the changed pointer position. For example, when the pointer 658 is changed to a position indicating “G”, the display color of the OCT cross-sectional image is set to G (green), and in the {R, G, B} format, {0, 0, 0} to { 0, 255, 0} is displayed as a single green image. In this case, the color of the IVUS cross-sectional image is not changed. That is, the color change is performed independently for each of the OCT cross-sectional image and the IVUS cross-sectional image.

If it is determined that the instruction from the user is neither the pointer 658 or 659, the process advances to step S1109 to determine whether the position of the pointer 656 or 657 has been changed. If it is determined that any of the positions has been changed, the process proceeds to step S1110, and the contrast of the target cross-sectional image is changed according to the changed pointer position. For example, when the pointer 656 is changed, only the contrast of the OCT cross-sectional image is changed, and the contrast of the IVUS cross-sectional image is not changed. That is, the contrast is also changed independently for each of the OCT sectional image and the IVUS sectional image.

If it is determined that the instruction from the user is neither the pointer 656 nor 657, the process proceeds to step S1111 and the corresponding process is executed. For example, when it is determined that the button 501 has been instructed, the mode is switched to the parallel display mode. If it is determined that the button 502 has been instructed, the instruction is ignored.

The alternate display mode in the embodiment has been described above. According to the alternate display mode of the above-described embodiment, the IVUS cross-sectional image and the OCT cross-sectional image are displayed alternately, so that the individual cross-sectional images can maintain the original contrast. Moreover, since alternate display can be performed at the speed and time ratio desired by the user, it is possible to focus on the relationship between both images and the cross-sectional image to be noticed without moving the viewpoint. In addition, regardless of the speed of the alternate display speed, one of the cross-sectional images desired by the user can be temporarily frozen and displayed, and a correct diagnosis can be performed.

Although the embodiment according to the present invention has been described above, the numerical values and display examples described in the above embodiment are merely examples, and the present invention is not limited thereto.

Further, various parameters set by the pointers 656 to 661 may be stored in a nonvolatile storage means such as a hard disk, and the stored parameters may be read and reset.

In the embodiment, the example of the apparatus having the OCT function and the IVUS function has been described. However, the embodiment can be applied to an apparatus that obtains cross-sectional images of the same living tissue with two or more different functional configurations. The present invention is not limited.

Also, as can be seen from the above embodiment, most of the processing related to the alternate display is performed by the signal processing unit 428 formed of a microprocessor. Accordingly, since the microprocessor realizes its function when the program is executed, the program naturally falls within the scope of the present invention. In particular, in the embodiment, the image diagnostic apparatus illustrated in FIG. 1 has been described as an example. However, the IVUS cross-sectional image information obtained by the image diagnostic apparatus illustrated in FIG. 1 is executed by a normal personal computer executing an application program. Alternatively, a storage medium (for example, a CDROM or a memory card) storing the OCT cross-sectional image information is accessed, and as a result, the read IVUS cross-sectional image information and OCT cross-sectional image information are realized as the user interface of the above embodiment. I do not care. In addition, the normal program is stored in a computer-readable storage medium such as a CD-ROM or DVD-ROM, and is set in a reading device (such as a CD-ROM drive) of the computer and copied or installed in the system. It is apparent that such a computer-readable storage medium falls within the scope of the present invention.

The present invention is not limited to the above embodiment, and various changes and modifications can be made without departing from the spirit and scope of the present invention. Therefore, in order to make the scope of the present invention public, the following claims are attached.

Claims (12)

  1. From a living tissue received by the ultrasonic transmission / reception unit, holding a probe having a transmission / reception unit in which an ultrasonic transmission / reception unit for transmitting / receiving ultrasonic waves and an optical transmission / reception unit for transmitting / receiving light are arranged rotatably and detachably. An ultrasonic diagnostic image and an optical cross-sectional image of the biological tissue using the reflected wave and the reflected light from the biological tissue received by the optical transceiver,
    Storage means for storing the generated ultrasonic cross-sectional image and the optical cross-sectional image;
    And a display control means for alternately displaying the ultrasonic cross-sectional image and the optical cross-sectional image stored in the storage means in one image display area along a time axis. .
  2. 2. The diagnostic imaging apparatus according to claim 1, further comprising user interface display means for displaying a user interface on the display screen.
  3. 3. The diagnostic imaging apparatus according to claim 2, wherein the user interface includes an operation unit for setting a minimum display time when the ultrasonic cross-sectional image and the optical cross-sectional image are alternately displayed.
  4. 4. The diagnostic imaging apparatus according to claim 2, wherein the user interface includes an operation unit for setting a display time ratio between the ultrasonic cross-sectional image and the optical cross-sectional image.
  5. 5. The user interface according to claim 2, wherein the user interface includes two operation units for independently setting contrasts of the ultrasonic cross-sectional image and the optical cross-sectional image. 6. Diagnostic imaging device.
  6. The said user interface contains two operation parts for setting the color of each of the said ultrasonic cross-sectional image and the said optical cross-sectional image independently, The any one of Claims 2 thru | or 5 characterized by the above-mentioned. Diagnostic imaging device.
  7. The user interface temporarily stops the alternate display, and continues to display the ultrasonic cross-sectional image in the image display region, and displays the optical cross-sectional image in the image display region. The diagnostic imaging apparatus according to claim 2, further comprising a button for continuing.
  8. From a living tissue received by the ultrasonic transmission / reception unit, holding a probe having a transmission / reception unit in which an ultrasonic transmission / reception unit for transmitting / receiving ultrasonic waves and an optical transmission / reception unit for transmitting / receiving light are arranged rotatably and detachably. A diagnostic method for generating an ultrasonic cross-sectional image and an optical cross-sectional image of the biological tissue using the reflected wave of the reflected light and the reflected light from the biological tissue received by the optical transceiver unit,
    Storing the generated ultrasonic cross-sectional image and the optical cross-sectional image in a storage means;
    A display control step of alternately displaying the ultrasonic cross-sectional image and the optical cross-sectional image stored in the storage means in one image display area along a time axis. Control method.
  9. A program for causing a computer to execute each step of the control method for the diagnostic imaging apparatus according to claim 8.
  10. An information processing apparatus that displays the ultrasonic cross-sectional image and the optical cross-sectional image obtained by an image diagnostic apparatus that generates an ultrasonic cross-sectional image and an optical cross-sectional image,
    Access means for accessing a storage medium for storing the ultrasonic cross-sectional image and the optical cross-sectional image;
    An information processing apparatus comprising: display control means for alternately displaying the ultrasonic cross-sectional image and the optical cross-sectional image read by the access means along a time axis in one image display area. .
  11. A method of controlling an information processing apparatus that displays an ultrasonic cross-sectional image and the ultrasonic cross-sectional image obtained by an image diagnostic apparatus that generates an optical cross-sectional image and the optical cross-sectional image,
    An access step of accessing a storage medium storing the ultrasonic cross-sectional image and the optical cross-sectional image;
    A display control step of alternately displaying the ultrasonic cross-sectional image and the optical cross-sectional image read in the access step along a time axis in one image display area. Control method.
  12. The program for making a computer perform each process of the control method of the information processing apparatus of Claim 11.
PCT/JP2012/006090 2012-09-25 2012-09-25 Diagnostic imaging device, information processing device, and method for controlling diagnostic imaging device and information processing device WO2014049634A1 (en)

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