WO2016136579A1 - Dispositif de diagnostic par imagerie, procédé de commande, programme, et support d'informations lisible par ordinateur correspondant - Google Patents

Dispositif de diagnostic par imagerie, procédé de commande, programme, et support d'informations lisible par ordinateur correspondant Download PDF

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Publication number
WO2016136579A1
WO2016136579A1 PCT/JP2016/054684 JP2016054684W WO2016136579A1 WO 2016136579 A1 WO2016136579 A1 WO 2016136579A1 JP 2016054684 W JP2016054684 W JP 2016054684W WO 2016136579 A1 WO2016136579 A1 WO 2016136579A1
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cross
image
sectional image
circularity
section
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PCT/JP2016/054684
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English (en)
Japanese (ja)
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淳也 古市
耕一 井上
聖 清水
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テルモ株式会社
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Priority to JP2017502309A priority Critical patent/JP6669720B2/ja
Publication of WO2016136579A1 publication Critical patent/WO2016136579A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/12—Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters

Definitions

  • the present invention relates to an image diagnostic apparatus, a control method thereof, a program, and a computer-readable storage medium.
  • an image diagnostic apparatus such as an optical coherence tomography (OCT: Optical Coherence Tomography) or intravascular ultrasound (IVUS) is used. It has become common. Further, as an improved type of OCT, an optical coherence tomography diagnostic device (SS-OCT: Optical coherence Tomography) using wavelength sweeping has been developed. Recently, an image diagnosis apparatus (an image diagnosis apparatus including an ultrasonic transmission / reception unit capable of transmitting / receiving ultrasonic waves and an optical transmission / reception unit capable of transmitting / receiving light) combining an IVUS function and an OCT function is also proposed. Has been.
  • One of the purposes of placing the stent is to secure blood flow in the stenotic region of the blood vessel. Therefore, the pre-operative diagnosis in the diagnostic apparatus is used for diagnosing the position, diameter, and length of the stenosis portion of the blood vessel. In addition, the dimensions and the like of the stent to be used are determined.
  • the diagnostic apparatus can generate a cross-sectional view of a blood vessel lumen, it can be diagnosed whether or not the blood vessel lumen surface has a shape deviating from a circle by looking at the cross section. .
  • the diagnosis is limited to the diagnosis of individual sections.
  • how long the stent is used and where the both ends of the stent are positioned are important. Therefore, a display format that is convenient for making these diagnoses is desired. .
  • the present invention has been made in view of such problems, and an object of the present invention is to provide a technique for visually displaying the circularity of the lumen surface along the blood vessel axis.
  • an image diagnostic apparatus of the present invention has the following configuration. That is, An image diagnostic apparatus for acquiring an image of a blood vessel lumen using a probe that accommodates an imaging core that emits and receives signals so as to be rotatable and movable along a rotation axis.
  • First image generation means for generating a cross-sectional image orthogonal to the rotation axis at each position along the rotation axis based on data obtained by rotating the imaging core and moving in the rotation axis direction
  • a second image generation unit configured to generate a cross-sectional image along the blood vessel axis based on data obtained by rotating the imaging core and moving the imaging core in the direction of the rotation axis
  • Calculating means for calculating a circularity indicating a circularity degree of a lumen surface in each cross-sectional image generated by the first image generating means
  • Display means for displaying the cross-sectional image generated by the second image generation means in association with the circularity calculated by the calculation means;
  • the circularity of the lumen surface can be visually and easily displayed along the blood vessel axis.
  • FIG. 1 is a diagram showing an example of the overall configuration of an image diagnostic apparatus 100 using wavelength sweeping according to an embodiment of the present invention.
  • the diagnostic imaging apparatus 100 includes a probe (or catheter) 101, a pullback unit 102, and an operation control device 103.
  • the pullback unit 102 and the operation control device 103 are connected by a cable 104 via a connector 105.
  • the cable 104 accommodates an optical fiber and various signal lines.
  • the probe 101 accommodates an optical fiber rotatably. At the tip of this optical fiber, the light (measurement light) transmitted from the operation control device 100 via the pullback unit 102 is transmitted in a direction substantially perpendicular to the central axis of the optical fiber, and the transmitted light An imaging core 250 having an optical transmission / reception unit for receiving reflected light from outside is provided.
  • the pullback unit 102 holds the optical fiber in the probe 101 via an adapter provided in the probe 101.
  • the imaging core provided at the tip of the probe 101 can be rotated by rotating the optical fiber in the probe 101 by driving a motor built in the pullback unit 102.
  • the pullback unit 102 also performs a process of driving a motor provided in the built-in linear drive unit to pull the optical fiber in the probe 101 at a predetermined speed (which is called a pullback unit).
  • the operation control device 103 has a function of comprehensively controlling the operation of the diagnostic imaging apparatus 100.
  • the operation control device 103 has, for example, a function of inputting various setting values based on user instructions into the device and a function of processing data obtained by measurement and displaying it as a tomographic image in the body cavity.
  • the operation control device 103 includes a main body control unit 111, a printer / DVD recorder 111-1, an operation panel 112, an LCD monitor 113, and the like.
  • the main body control unit 111 generates an optical tomographic image.
  • the optical tomographic image generates interference light data by causing interference between reflected light obtained by measurement and reference light obtained by separating light from the light source, and is generated based on the interference light data. It is generated by processing the line data.
  • the printer / DVD recorder 111-1 prints the processing result in the main body control unit 111 or stores it as data.
  • the operation panel 112 is a user interface through which a user inputs various setting values and instructions.
  • the LCD monitor 113 functions as a display device and displays, for example, a tomographic image generated by the main body control unit 111.
  • Reference numeral 114 denotes a mouse as a pointing device (coordinate input device).
  • the image diagnostic apparatus includes an optical coherent tomographic image diagnostic apparatus (OCT) and an optical coherent tomographic image diagnostic apparatus (SS-OCT) using a wavelength sweep.
  • OCT optical coherent tomographic image diagnostic apparatus
  • SS-OCT optical coherent tomographic image diagnostic apparatus
  • reference numeral 201 denotes a signal processing unit that controls the entire diagnostic imaging apparatus, and is composed of several circuits including a microprocessor.
  • Reference numeral 210 denotes a non-volatile storage device represented by a hard disk, which stores various programs and data files executed by the signal processing unit 201.
  • Reference numeral 202 denotes a memory (RAM) provided in the signal processing unit 201.
  • a wavelength swept light source 203 is a light source that repeatedly generates light having a wavelength that changes within a preset range along the time axis.
  • the light output from the wavelength swept light source 203 is incident on one end of the first single mode fiber 271 and transmitted toward the distal end side.
  • the first single mode fiber 271 is optically coupled to the fourth single mode fiber 275 at an intermediate optical fiber coupler 272.
  • the light emitted from the optical fiber coupler 272 in the first single mode fiber 271 to the distal end side is guided to the second single mode fiber 273 via the connector 105.
  • the other end of the second single mode fiber 273 is connected to the optical rotary joint 230 in the pullback unit 102.
  • the probe 101 has an adapter 101 a for connecting to the pullback unit 102. Then, the probe 101 is stably held by the pullback unit 102 by connecting the probe 101 to the pullback unit 102 by the adapter 101a. Furthermore, the end of the third single mode fiber 274 rotatably accommodated in the probe 101 is connected to the optical rotary joint 230. As a result, the second single mode fiber 273 and the third single mode fiber 274 are optically coupled. At the other end of the third single mode fiber 274 (on the leading portion side of the probe 101), an imaging core 250 on which a lens that emits light in a direction substantially perpendicular to the rotation axis is mounted.
  • the light emitted from the wavelength swept light source 203 passes through the first single mode fiber 271, the second single mode fiber 273, and the third single mode fiber 274 to the end of the third single mode fiber 274. It is guided to the provided imaging core 250.
  • the image core 250 emits this light in a direction perpendicular to the axis of the fiber, receives the reflected light, and the received reflected light is led in reverse and returned to the operation control device 103.
  • an optical path length adjustment mechanism 220 that finely adjusts the optical path length of the reference light is provided at the opposite end of the fourth single mode fiber 275 coupled to the optical fiber coupler 272.
  • the optical path length variable mechanism 220 functions as an optical path length changing unit that changes the optical path length corresponding to the variation in length so that the variation in length of each probe 101 can be absorbed when the probe 101 is replaced.
  • a collimating lens 225 located at the end of the fourth single mode fiber 275 is provided on a movable uniaxial stage 224 as indicated by an arrow 226 in the optical axis direction.
  • the uniaxial stage 224 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 probe 101. Further, the uniaxial stage 224 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 224, and the light reflected by the mirror 223 via the grating 221 and the lens 222 is again guided to the fourth single mode fiber 275, and the first optical fiber coupler 272
  • the light obtained from the single mode fiber 271 side is mixed and received by the photodiode 204 as interference light.
  • the interference light received by the photodiode 204 in this way is photoelectrically converted, amplified by the amplifier 205, and then input to the demodulator 206.
  • the demodulator 206 performs demodulation processing for extracting only the signal portion of the interfered light, and its output is input to the A / D converter 207 as an interference light signal.
  • the A / D converter 207 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 assumption that about 90% of the wavelength sweep cycle (25 ⁇ sec) is extracted as 2048 digital data when the wavelength sweep repetition frequency is 40 kHz. There is no particular limitation.
  • the line-by-line interference light data generated by the A / D converter 207 is input to the signal processing unit 201 and temporarily stored in the memory 202.
  • the interference light data is subjected to frequency decomposition by FFT (Fast Fourier Transform) to generate data in the depth direction (line data), and this is coordinate-converted to obtain data at each position in the blood vessel.
  • FFT Fast Fourier Transform
  • An optical section image is constructed and output to the LCD monitor 113 at a predetermined frame rate.
  • the signal processing unit 201 is further connected to an optical path length adjustment driving unit 209 and a communication unit 208.
  • the signal processing unit 201 controls the position of the uniaxial stage 224 (optical path length control) via the optical path length adjustment driving unit 209.
  • the communication unit 208 incorporates several drive circuits and communicates with the pullback unit 102 under the control of the signal processing unit 201. Specifically, from the encoder unit 242 for detecting the rotational position of the radial motor by supplying a driving signal to the radial scanning motor for rotating the third single mode fiber by the optical rotary joint in the pullback unit 102. And the supply of a drive signal to the linear drive unit 243 for pulling the third single mode fiber 274 at a predetermined speed.
  • the above processing in the signal processing unit 201 is also realized by a predetermined program being executed by a computer.
  • the signal processing unit 201 drives the wavelength swept light source 203 to drive the radial scanning motor 241 and the linear driving unit 243 (hereinafter, the radial scanning motor 241 and the linear driving unit). (Light irradiation and light reception processing by driving 243 is called scanning).
  • the wavelength swept light is supplied from the wavelength swept light source 203 to the imaging core 250 through the path as described above.
  • the imaging core 250 at the distal end position of the probe 101 rotates and moves along the rotation axis
  • the imaging core 250 rotates while moving along the blood vessel axis. Light is emitted to the blood vessel lumen surface and its reflected light is received.
  • FIG. 1 is a view for explaining the reconstruction processing of the cross-sectional image of the lumen surface 301 orthogonal to the blood vessel axis of the blood vessel in which the imaging core 250 is located.
  • the measurement light is transmitted and received a plurality of times.
  • data of one line in the direction of irradiation with the light can be obtained. Therefore, 512 interference light data extending radially from the rotation center 302 can be obtained by transmitting and receiving light, for example, 512 times during one rotation.
  • the 512 pieces of interference light data are subjected to fast Fourier transform, and radial radial line data is generated from the center of rotation.
  • the line data is dense in the vicinity of the rotation center position and becomes sparse with distance from the rotation center position. Therefore, the pixels in the vacant space of each line are generated by performing a well-known interpolation process to generate a blood vessel cross-sectional image that can be seen by humans.
  • the signal processing unit 201 performs the process of reconstructing the blood vessel cross-sectional image in this way.
  • the number of each blood vessel cross-sectional image (slice No.), the lumen area S of the blood vessel cross-sectional image, and the lumen area S
  • the degree of circularity C which is an index value indicating how close the shape is to a perfect circle, is obtained.
  • the algorithm for calculating the circularity C is not particularly limited, but in the embodiment, D2 / D1, which is a ratio of the major axis D1 to the minor axis D2 in the lumen area, is obtained as the circularity C as an example.
  • a lesion site such as stenosis is very likely to be a site having a small lumen area S or a small circularity C.
  • the slice number, the lumen area S, and the circularity C are collectively referred to as cross-sectional feature information.
  • the signal processing unit 201 calculates corresponding cross-sectional feature information, and stores the cross-sectional image and the cross-sectional feature information in the memory 202 in association with each other.
  • the lumen area S is obtained by, for example, counting the total number of inner pixels from the lumen surface toward the rotation center of the imaging core 250 and multiplying the coefficient result by a preset coefficient.
  • the method for obtaining the cavity area may be obtained by an algorithm other than this.
  • the major axis D1 is the distance between the two points when the distance between the two points on the lumen surface is maximum.
  • the minor axis D2 is a distance between two points where the perpendicular passing through the center point of the major axis D1 and the lumen surface intersect. Further, the longest diameter and the shortest diameter passing through the center of gravity of the closed curve configured as the lumen surface may be used.
  • the signal processing unit 201 connects the generated blood vessel cross-sectional images 401 to each other along the blood vessel axis as shown in FIG. A blood vessel image 402 can be obtained. It should be noted that the center position of the two-dimensional blood vessel cross-sectional image coincides with the rotation center position of the imaging core 250, but is not the center position of the blood vessel cross-section.
  • a cross-sectional image cut along the arrow A in the three-dimensional blood vessel image 402 (a cross-sectional image cut along a plane parallel to the blood vessel axis) is hereinafter referred to as a vertical cross-sectional image and cut along a plane perpendicular to the blood vessel axis in FIG. Differentiate from blood vessel cross-sectional images.
  • the three-dimensional blood vessel image 402 is reconstructed and then the longitudinal section image is generated.
  • certain line data (when the two-dimensional section image is constructed as shown in FIG. 3)
  • line data of 0 ° For example, a single piece of data represented by line data of 0 °
  • the opposite 180 °
  • a stenotic portion is identified by a user (doctor or the like). Are displayed in an easy-to-understand manner.
  • FIG. 6A shows an initial GUI 600 displayed on the monitor 113 when the scanning process is finished.
  • the GUI 600 includes display areas indicated by reference numerals 610, 620, and 630.
  • a vertical cross-sectional image (a blood vessel cross-sectional image cut along a plane along the blood vessel axis) is displayed.
  • a stenosis index image representing the degree of stenosis from two index values of area S and circularity C is displayed.
  • the display area 630 displays a blood vessel cross-sectional image (see FIG. 3) cut along a plane perpendicular to the blood vessel axis in the line segment 612 indicated by the marker 611 displayed in the display area 610.
  • the scale 640 was displayed between them.
  • Reference numerals 650a to 650c indicating the illustrated range will be described later.
  • the signal processing unit 201 calculates cross-sectional feature information including the lumen area S and the circularity C for each. In this process, the signal processing unit 201 obtains the maximum lumen area Smax. Then, the lumen area S / Smax is calculated for each cross-sectional image. That is, the maximum lumen area in the pullback scanned range is set to 1, and the area of each cross-sectional image is normalized to a range of 0 to 1. In addition, the signal processing unit 210 obtains a slice No that minimizes the circularity C.
  • the signal processing unit 201 is a color palette (in the case of illustration) with respect to two coordinate axes having a lumen area S after normalization (maximum value is 1) and circularity C (also maximum value is 1). Prepare 4 ⁇ 4 color palettes P00 to P33).
  • one palette is determined from the lumen area S after normalization of each cross-sectional image and the circularity C, and the color of the vertical line segment in the display area 620 is determined using the determined palette. For example, when the area S after normalization of a certain blood vessel cross-sectional image is 0.74 and the circularity C is 0.52, it is determined that the palette P22 is used from the coordinates indicated by these two, and the palette A vertical line having the color P22 is drawn at a corresponding position in the display area 620.
  • a stenosis index image to be displayed in the display area 620 in FIG. 6A is generated.
  • a portion to be drawn with the determined palette is not a “vertical line” but a rectangle (rectangle). That is, when the vertical size of the display area 620 is H, the horizontal size is W, and the total number of cross-sectional images corresponding to the horizontal size is N, the area drawn with the determined palette is the vertical direction H and the horizontal direction. This is a rectangular area defined by W / N. Therefore, the rectangular area is filled with the determined palette color.
  • the user can freely change the position of the marker 611 in the display area 610 by operating the mouse 114.
  • the signal processing unit 201 reads the corresponding cross-sectional image and its cross-sectional feature information from the memory 202 based on the changed position of the marker 611, and updates the display area 630.
  • the signal processing unit 201 prepares two threshold values Th1 and Th2 (where Th2 ⁇ Th1) with respect to the circularity C, and once sandwiches the point where the circularity C has decreased to less than the threshold Th2, the threshold value Th1 or less.
  • the section is determined as a lesion section, and the section is notified to the user.
  • Reference numerals 650a, 650b, and 650c in FIG. 6A represent lesion sections.
  • a cross-sectional image to be displayed in the display area 630 at an initial stage when displaying the GUI of FIG. 6A is detected in each of a plurality of detected lesion sections, and a frame having the smallest blood vessel area is detected.
  • a cross-sectional image showing the smallest blood vessel diameter was used.
  • the cross-sectional feature information (area S before normalization, circularity C, major axis D1, minor axis D2) in the sectional image having the minimum circularity C is displayed together.
  • the signal processing unit 201 displays the marker 611 and the vertical line 612 at the corresponding position in the display area.
  • the cross-sectional image displayed in the display area 630 in the initial stage of FIG. 6A may be a cross-sectional image having a minimum circularity.
  • the processing procedure of the signal processing unit 201 will be described next with reference to the flowchart of FIG. In the following description, it is assumed that the probe 101 has already been inserted into the target blood vessel affected area of the patient.
  • step S101 it is determined whether or not there is an instruction to start scanning from the operation panel 112. If it is determined that a scan start instruction has been issued, the process proceeds to step S102, and a pull-back scan process is executed.
  • the signal processing unit 201 causes the pull-back unit 102 to rotate the imaging core 250 at a preset speed via the communication unit 208 and perform a process of moving the imaging core 250 backward at a predetermined speed.
  • step S103 it is determined whether or not the movement amount of the imaging core 250 relative to the blood vessel axis has reached the planned movement amount. If not, the pullback scan is continued.
  • step 104 the interference light data accumulated in the memory 202 is subjected to FFT (Fast Fourier Transform), frequency-resolved, and the depth direction Data (line data) is generated, and the result is used to reconstruct a cross-sectional image orthogonal to the blood vessel axis.
  • step S105 cross-sectional feature information (lumen area S, major axis D1, minor axis D2, and circularity C) is calculated for the reconstructed cross-sectional image, and the cross-sectional image and the cross-sectional feature information are associated with each other and stored in memory. 202.
  • step S106 it is determined whether or not the reconstruction processing for all the cross-sectional images has been completed. If not, the processing in steps 104 and 105 is repeated.
  • a palette for indicating a stenosis index for each cross-sectional image is determined based on the image feature information of each cross-sectional image.
  • a section having a threshold value Th1 or less sandwiching a point where the circularity becomes smaller than the threshold value Th2 is determined as a lesion section, and the minimum lumen in each lesion section is determined. Find the area.
  • step S108 a longitudinal cross-sectional image cut along a plane parallel to the blood vessel axis (an arrow indicating a lesion interval is also synthesized), a stenosis index image determined by a palette of each cross-sectional image, and each obtained lesion interval
  • the tomographic images showing the minimum areas are displayed in a layout as shown in FIG. 6A, and the marker 611 and the line segment 612 are drawn freely at the displayed cross-sectional image positions.
  • FIG. 6A it is possible to provide a GUI that can easily grasp how a lesion site exists along the blood vessel axis, taking into account the lumen area and circularity. . Further, even if no particular operation is performed, sections that are expected to be lesions are displayed according to the circularity, the minimum lumen area in each section is obtained, and a cross-sectional image having the minimum lumen area between each section is obtained. Since it is displayed and the lumen area and circularity at that position are displayed, it is also possible to easily determine where the region to be included when placing the stent should be.
  • both ends of the stent when the stent is placed are desired to be healthy blood vessels, that is, portions having a circularity close to a perfect circle and a large area.
  • the display of FIG. 6A it is possible to easily understand the position where both the lumen area and the circularity are high, and it is possible to easily know the length by comparing with the scale.
  • the cross-sectional image to be displayed may be displayed in the display area 630. This is because it is usually desirable that the positions of both ends of the stent when the stent is placed be healthy blood vessel positions (positions with a high degree of circularity).
  • one pallet to be used is determined based on two index values of lumen area and circularity.
  • one pallet represents the lumen area S and the circularity C
  • the user needs to be familiar with the relationship.
  • the GUI shown in FIG. 6B may be used instead of FIG. 6A.
  • the display area 622 for displaying the circularity index and the display area 623 for displaying the lumen area index are displayed independently, only the brightness (or density) is high and low for the user. It is possible to grasp the degree of and easy to understand.
  • the degree of circularity and the area of the lumen are indicated by palettes and shades. However, since the degree of circularity and the area of the lumen have already been calculated as numerical values, they are represented by a line graph or the like. It doesn't matter.
  • the section length may be displayed together.
  • branches in the blood vessel to be diagnosed there may be branches in the blood vessel to be diagnosed.
  • the circularity may not be measured. Therefore, the branch portion may be excluded from the target for calculating the circularity.
  • the condition is that the probe is inserted into the patient's blood vessel and scanned before displaying the GUI of FIGS. 6A and 6B.
  • the data obtained by scanning is stored in a storage medium such as a hard disk. 6A and 6B
  • the GUI shown in FIGS. 6A and 6B may be displayed after a certain period of time. In this case, after the data stored in the storage medium is read out to the memory 202, the processing after S104 in FIG. 7 is performed.
  • a part of the characteristic part in the embodiment is due to the signal processing unit 201 including at least a microprocessor. Since the microprocessor realizes its function by executing a program, the program naturally falls within the scope of the present invention. Further, the program is usually stored in a computer-readable storage medium such as a CD-ROM or DVD-ROM, and is set in a reading device (CD-ROM drive or the like) included in the computer and copied or installed in the system. It is obvious that such a computer-readable storage medium is also within the scope of the present invention.

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Abstract

La présente invention vise à afficher les degrés de circularité d'une surface luminale d'un vaisseau sanguin le long de l'axe de vaisseau sanguin d'une manière visuellement facile à comprendre. À cet effet, l'invention concerne une image tomographique prise le long de l'axe de vaisseau sanguin, qui est produite sur la base de données obtenues par rotation d'un noyau d'imagerie et déplacement du noyau d'imagerie dans la direction d'axe de rotation. Simultanément, une image indiquant les degrés de circularité dans des images tomographiques prises perpendiculairement à l'axe de vaisseau sanguin est affichée en parallèle avec l'image tomographique affichée.
PCT/JP2016/054684 2015-02-25 2016-02-18 Dispositif de diagnostic par imagerie, procédé de commande, programme, et support d'informations lisible par ordinateur correspondant WO2016136579A1 (fr)

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JP2019150574A (ja) * 2018-03-05 2019-09-12 リオン株式会社 ３次元形状データ作成方法、及び３次元形状データ作成システム
JP2020152790A (ja) * 2019-03-19 2020-09-24 互応化学工業株式会社 水系離型剤及び剥離部材
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JP7493524B2 (ja) 2018-10-26 2024-05-31 コーニンクレッカ フィリップス エヌ ヴェ 管腔内超音波イメージングのためのグラフィカル長手方向表示、並びに、関連するデバイス、システム、及び方法

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JP7236689B2 (ja) 2018-03-05 2023-03-10 リオン株式会社 ３次元形状データ作成システムの作動方法、及び３次元形状データ作成システム
JP2022509401A (ja) * 2018-10-26 2022-01-20 コーニンクレッカ フィリップス エヌ ヴェ 管腔内超音波イメージングのためのグラフィカル長手方向表示、並びに、関連するデバイス、システム、及び方法
JP7493524B2 (ja) 2018-10-26 2024-05-31 コーニンクレッカ フィリップス エヌ ヴェ 管腔内超音波イメージングのためのグラフィカル長手方向表示、並びに、関連するデバイス、システム、及び方法
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