CN117146700B - OCT equipment optical path calibration method and device and OCT equipment - Google Patents

OCT equipment optical path calibration method and device and OCT equipment Download PDF

Info

Publication number
CN117146700B
CN117146700B CN202311417334.4A CN202311417334A CN117146700B CN 117146700 B CN117146700 B CN 117146700B CN 202311417334 A CN202311417334 A CN 202311417334A CN 117146700 B CN117146700 B CN 117146700B
Authority
CN
China
Prior art keywords
optical path
oct
reference arm
column
oct image
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Active
Application number
CN202311417334.4A
Other languages
Chinese (zh)
Other versions
CN117146700A (en
Inventor
张仕瑞
武西宁
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Tianjin Hengyu Medical Technology Co ltd
Original Assignee
Tianjin Hengyu Medical Technology Co ltd
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Tianjin Hengyu Medical Technology Co ltd filed Critical Tianjin Hengyu Medical Technology Co ltd
Priority to CN202311417334.4A priority Critical patent/CN117146700B/en
Publication of CN117146700A publication Critical patent/CN117146700A/en
Application granted granted Critical
Publication of CN117146700B publication Critical patent/CN117146700B/en
Active legal-status Critical Current
Anticipated expiration legal-status Critical

Links

Classifications

    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/0209—Low-coherence interferometers
    • G01B9/02091—Tomographic interferometers, e.g. based on optical coherence
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00—Measuring instruments characterised by the use of optical techniques
    • G01B9/02—Interferometers
    • G01B9/02055—Reduction or prevention of errors; Testing; Calibration
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/02—Operational features
    • A61B2560/0223—Operational features of calibration, e.g. protocols for calibrating sensors

Abstract

The application provides an OCT device optical path calibration method, an OCT device optical path calibration device and an OCT device. The optical path calibration method of the OCT equipment comprises the following steps: adjusting a reference arm of the OCT apparatus to a normal optical path range; wherein when the reference arm is in a normal optical path range, the current image of the OCT apparatus is a positive image; identifying position information of the outer wall of the catheter for the currently acquired target OCT image; determining the distance to be moved of the reference arm according to the position information and preset position information corresponding to the optical path zero point; and controlling an optical path motor to drive the reference arm to move towards a first designated direction by the distance so that the outer wall reaches a position corresponding to the preset position information and the reference arm reaches an optical path zero position. The optical path calibration method and device for the OCT equipment and the OCT equipment can improve the efficiency of optical path calibration.

Description

OCT equipment optical path calibration method and device and OCT equipment
Technical Field
The present disclosure relates to the technical field of medical devices, and in particular, to an OCT device optical path calibration method and apparatus, and an OCT device.
Background
The development of optical coherence tomography (Optical Coherence Tomography, OCT) technology has had a profound impact on the medical and other scientific fields. In performing an acquisition using an OCT apparatus, it is necessary to connect a catheter (disposable acquisition catheter) to the OCT apparatus first. However, since the dimensions of each catheter are not exactly uniform, the optical path length is calibrated each time. Manual calibration can increase patient and physician latency and is inefficient.
Disclosure of Invention
In view of the foregoing, the present application provides an OCT apparatus optical path calibration method, apparatus, and device for rapidly performing optical path calibration and improving calibration efficiency.
Specifically, the application is realized by the following technical scheme:
a first aspect of the present application provides an OCT apparatus optical path calibration method, which is applied to an OCT apparatus, in which a catheter is connected to an end of a sample arm; the method comprises the following steps:
adjusting a reference arm of the OCT apparatus to a normal optical path range; wherein when the reference arm is in a normal optical path range, the current image of the OCT apparatus is a positive image;
identifying positional information of an outer wall of the catheter for a currently acquired target OCT image;
Determining the distance to be moved of the reference arm according to the position information and preset position information corresponding to the optical path zero point;
and controlling an optical path motor to drive the reference arm to move towards a first designated direction by the distance so that the outer wall reaches a position corresponding to the preset position information and the reference arm reaches an optical path zero position.
A second aspect of the present application provides an OCT apparatus optical path calibration device applied to an OCT apparatus having a catheter connected to an end of a sample arm thereof; the device comprises an adjusting module, a processing module, a determining module and a calibrating module, wherein,
the adjusting module is used for adjusting the reference arm of the OCT equipment to a normal optical path range; wherein when the reference arm is in a normal optical path range, the current image of the OCT apparatus is a positive image;
the processing module is used for identifying the position information of the outer wall of the catheter aiming at the currently acquired target OCT image;
the determining module is used for determining the distance to be moved of the reference arm according to the position information and preset position information corresponding to the optical path zero point;
the calibration module is used for controlling the optical path motor to drive the reference arm to move towards a first appointed direction for the distance, so that the outer wall reaches a position corresponding to the preset position information, and the reference arm reaches an optical path zero position.
A third aspect of the present application provides an OCT apparatus comprising a memory, a processor and a computer program stored on the memory and executable on the processor, the processor implementing the steps of any one of the methods provided in the first aspect of the present application when the program is executed.
A fourth aspect of the present application provides a storage medium having stored thereon a program which when executed by a processor performs the steps of any of the methods provided in the first aspect of the present application.
According to the optical path calibration method and device for the OCT equipment and the OCT equipment, when the reference arm of the OCT equipment is in the normal optical path range, the current image formed by the OCT equipment is a positive image, and further the position information of the outer wall of the catheter is identified according to the current acquired target OCT image, so that the distance to be moved by the reference arm is determined according to the position information and the preset position information corresponding to the optical path zero point, and the optical path motor is controlled to drive the reference arm to move the distance towards the first appointed direction, so that the outer wall reaches the position corresponding to the preset position information and the reference arm reaches the optical path zero point. Therefore, the reference arm is firstly adjusted to a normal optical path range through rough calibration, the position information of the outer wall of the catheter is further identified, the distance to be moved of the reference arm is determined according to the position information and the preset position information of the optical path zero point, the movement of the reference arm is controlled according to the distance, the purpose of automatic calibration is achieved, the optical path calibration can be rapidly carried out, the waiting time of a patient and a main doctor can be reduced, and the calibration efficiency is improved.
Drawings
Fig. 1 is a schematic structural view of an OCT apparatus according to an exemplary embodiment of the present application;
fig. 2 is a flowchart of an embodiment of an optical path calibration method of an OCT apparatus provided in the present application;
fig. 3 is a flowchart of a second embodiment of an optical path calibration method of an OCT apparatus provided in the present application;
fig. 4 is a flowchart of a third embodiment of an optical path calibration method of an OCT apparatus provided in the present application;
FIG. 5 is a graph showing the result of identifying interference areas according to an exemplary embodiment of the present application;
FIG. 6 is a graph illustrating the identification of artifact regions according to an exemplary embodiment of the present application;
FIG. 7 is a graph showing the recognition result of a highlight region according to an exemplary embodiment of the present application;
fig. 8 is a hardware configuration diagram of an OCT apparatus in which the optical path calibration device of the OCT apparatus provided in the present application is located;
fig. 9 is a schematic structural diagram of an embodiment one of an optical path calibration device of an OCT apparatus provided in the present application.
Detailed Description
Reference will now be made in detail to exemplary embodiments, examples of which are illustrated in the accompanying drawings. When the following description refers to the accompanying drawings, the same numbers in different drawings refer to the same or similar elements, unless otherwise indicated. The implementations described in the following exemplary examples are not representative of all implementations consistent with the present application.
The terminology used in the present application is for the purpose of describing particular embodiments only and is not intended to be limiting of the present application. As used in this application, the singular forms "a", "an" and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise. It should also be understood that the term "and/or" as used herein refers to and encompasses any or all possible combinations of one or more of the associated listed items.
It should be understood that although the terms first, second, third, etc. may be used herein to describe various information, these information should not be limited by these terms. These terms are only used to distinguish one type of information from another. For example, a first message may also be referred to as a second message, and similarly, a second message may also be referred to as a first message, without departing from the scope of the present application. The word "if" as used herein may be interpreted as "at … …" or "at … …" or "responsive to a determination", depending on the context.
The application provides an OCT equipment optical path calibration method, an OCT equipment optical path calibration device and an OCT equipment, which are used for rapidly carrying out optical path calibration and improving the calibration efficiency.
According to the OCT equipment optical path calibration method, device and equipment, when the reference arm of the OCT equipment is in the normal optical path range, the current image of the OCT equipment is a positive image, and further the position information of the outer wall of the catheter is identified according to the current acquired target OCT image, so that the distance to be moved by the reference arm is determined according to the position information and the preset position information corresponding to the optical path zero point, and the optical path motor is controlled to drive the reference arm to move towards the first appointed direction for the distance, so that the outer wall reaches the position corresponding to the preset position information and the reference arm reaches the optical path zero point. Therefore, the reference arm is firstly adjusted to a normal optical path range through rough calibration, the position information of the outer wall of the catheter is further obtained through recognition, the distance to be moved of the reference arm is determined according to the position information and the preset position information of the optical path zero point, the movement of the reference arm is controlled according to the distance, the purpose of automatic calibration is achieved, the optical path calibration can be rapidly carried out, the waiting time of a patient and a main doctor can be reduced, and the calibration efficiency is improved.
Specific examples are given below to describe the technical solutions of the present application in detail.
Before describing the optical path calibration method of the OCT equipment, the OCT equipment is briefly described.
Fig. 1 is a schematic structural diagram of an OCT apparatus according to an exemplary embodiment of the present application. Referring to fig. 1, the oct apparatus includes a light source 1, a coupler 2, a reflecting mirror 3, an optical path motor 5, a catheter control device 6 (for connecting a catheter), a photoelectric balance detector/spectrometer 7, and a computer 8, wherein,
light source 1: for providing a light source for an optical coherence tomography device;
coupler 2: the light source is used for dividing the light source into two paths, wherein one path enters the reference arm, and the other path enters the sample arm;
reference arm: comprises a reflecting mirror 3 and an optical path motor 5;
sample arm: comprises a catheter control device 6 and a catheter connected to the catheter control device 6;
photoelectric balance detector/spectrometer 7: converting the interference signal into an electrical signal;
computer 8: the photoelectric balance detector/spectrometer comprises a digital acquisition card and an image acquisition card, wherein the digital acquisition card acquires an electric signal output by the photoelectric balance detector/spectrometer 7, and then outputs the electric signal to a digital image through the image acquisition card for storage and output.
Fig. 2 is a flowchart of an embodiment of an optical path calibration method of an OCT apparatus provided in the present application. Referring to fig. 2, the method includes:
s201, adjusting a reference arm of the OCT device to a normal optical path range; wherein the OCT apparatus currently forms an image that is positive when the reference arm is in a normal optical path range.
The optical path calibration method of the OCT apparatus provided in the present embodiment is applied to the OCT apparatus, specifically, referring to fig. 1, to a computer in the OCT apparatus.
It should be noted that, when the OCT apparatus is imaging, the reference arm may be in a mirror image optical path range or a normal optical path range, where when the reference arm is in the normal optical path range, the image currently formed by the OCT apparatus is a positive image; further, when the reference arm is in the mirror image optical path position, the image currently formed by the OCT apparatus is a mirror image, an inverse image.
In particular, the position of the reflecting mirror 3 can be controlled by the optical path motor 5, so that the optical path of the reference arm can be adjusted, and the reference arm of the OCT apparatus is in the normal optical path range. The specific implementation principle of this step will be described in detail in the following embodiments, which are not repeated here.
S202, identifying the position information of the outer wall of the catheter according to the currently acquired target OCT image.
In particular, image recognition techniques can be used to identify positional information of the outer wall of the catheter from the target OCT image.
For example, in one possible implementation, the target OCT image is the original OCT image acquired, at which time the outer wall of the catheter is a bright vertical line in the target OCT image, and the position information of the bright vertical line can be represented by the column coordinates of the pixel where the vertical line is located, e.g., identified, determinedThe position information of the outer wall of the catheter is recorded as。
S203, determining the distance to be moved of the reference arm according to the position information and preset position information corresponding to the optical path zero point.
The preset position information corresponding to the optical path zero point refers to position information corresponding to a position where the outer wall of the catheter should be located in the formed OCT image (the acquired original OCT image) when the reference arm is located at the optical path zero point position (the position where the reference arm is located when the optical path difference between the light returned by the reference arm and the light returned by the sample arm is within the image depth range). For example, in one embodiment, the preset position information corresponding to the optical path zero point is a column c.
It should be noted that, the distance to be moved by the reference arm refers to the distance to be moved by the optical path motor driving the mirror 3.
Specifically, in an embodiment, determining, according to the position information and preset position information corresponding to the optical path zero point, the distance to be moved by the reference arm may include:
(1) And determining the pixel distance to be moved by the reference arm according to the position information and the preset position information.
In particular, the pixel distance to be moved by the reference arm can be calculated according to the following formula:
，
wherein,for the pixel distance to be moved of the reference arm c is the preset position information, +.>Is the positional information of the outer wall of the catheter.
(2) And determining the distance to be moved of the reference arm corresponding to the pixel distance according to the corresponding relation between the predetermined pixel distance and the reference arm movement distance.
It should be noted that, the correspondence between the predetermined pixel distance and the reference arm moving distance may be predetermined as follows: moving the reference arm, recording the moving distance U and the number V of pixels corresponding to the movement of the target pattern (for example, in one embodiment, the target image is the outer wall of the catheter) in the OCT image, obtaining a plurality of groups of corresponding values (U, V) by moving the reference arm for a plurality of times, and finally obtaining the corresponding relation by adopting a function fitting mode.
In a specific implementation, for example, in one possible implementation, the predetermined correspondence between the pixel distance and the reference arm movement distance is a functional relationship, where the pixel distance may be substituted into the functional relationship, and the distance to be moved by the reference arm is calculated.
S204, controlling an optical path motor to drive the reference arm to move towards a first appointed direction for the distance, so that the outer wall reaches a position corresponding to the preset position information, and the reference arm reaches an optical path zero position.
It should be noted that, the first designated direction is a direction pointing from the column where the outer wall of the catheter is located to the column corresponding to the preset position information.
Specifically, after the distance to be moved by the reference arm is calculated according to the preset position information corresponding to the outer wall of the catheter and the optical path zero point, in this step, the optical path motor 5 is controlled to drive the reference arm to move towards the first designated direction by the distance, after the reference arm moves, the outer wall of the catheter reaches the position corresponding to the preset position information, and accordingly, at the moment, the reference arm reaches the optical path zero point position, and the optical path calibration is completed.
According to the optical path calibration method for the OCT equipment, when the reference arm of the OCT equipment is in the normal optical path range, the current image of the OCT equipment is a positive image, and further, the position information of the outer wall of the catheter is identified according to the current acquired target OCT image, so that the distance to be moved by the reference arm is determined according to the position information and the preset position information corresponding to the optical path zero point, and the optical path motor is controlled to drive the reference arm to move towards the first designated direction for the distance, so that the outer wall reaches the position corresponding to the preset position information and the reference arm reaches the optical path zero point. Therefore, the reference arm is firstly adjusted to a normal optical path range through rough calibration, the position information of the outer wall of the catheter is further identified, the distance to be moved of the reference arm is determined according to the position information and the preset position information of the optical path zero point, the movement of the reference arm is controlled according to the distance, the purpose of automatic calibration is achieved, the optical path calibration can be rapidly carried out, the waiting time of a patient and a main doctor can be reduced, and the calibration efficiency is improved.
Fig. 3 is a flowchart of a second embodiment of an optical path calibration method of an OCT apparatus provided in the present application. Referring to fig. 3, on the basis of the above, adjusting the reference arm of the OCT apparatus to a normal optical path range includes:
s301, controlling the optical path motor to drive the reference arm to move towards a second designated direction.
The second direction is determined according to the actual situation, and is not limited in this embodiment. In this step, the optical path motor is controlled to drive the reference arm to move towards the second designated direction, mainly for the purpose of enabling the reference arm to perform heuristic movement, and then comparing OCT images formed before and after the heuristic movement to determine whether the reference arm is currently in a normal optical path range. The second predetermined direction is taken as an optical path shortening direction as an example.
S302, determining the actual size change trend of the target pattern in the second OCT image relative to the target pattern in the first OCT image according to the first OCT image acquired before the optical path motor moves and the second OCT image acquired after the optical path motor moves.
For example, in one possible implementation, the target pattern may be identified from the first OCT image and the second OCT image respectively based on an image identification technique, and further, the sizes of the two target patterns are compared, so as to obtain the actual size change trend of the target pattern before and after the movement.
Optionally, in a possible implementation manner of the present application, when the first OCT image and the second OCT image are both acquired original OCT images, determining a trend of a change in a actual size of a target pattern in the second OCT image relative to the target pattern in the first OCT image may include:
(1) And calculating the average value of the pixel values of each column of pixels in the first OCT image aiming at the first OCT image to obtain a first row vector formed by the average value of the pixel values of each column of pixels.
Specifically, for example, in one embodiment, the first OCT image is recorded as(indicating that the first OCT image comprisesIndividual pixels), the mean of the pixel values for each column of pixels in the first OCT image can be calculated using the following formula:
，
wherein,first OCT image +.>An average of pixel values of the column pixels; />First OCT image +.>Line->Pixel values for column pixels.
In connection with this example, for the first row vectorIndicating (I)>In other words, the first row vector includes P elements, the P-th element of which is the average of the pixel values of the P-th column pixels.
(2) And carrying out smoothing processing on the first row vector, and determining a first column coordinate corresponding to the element with the largest median in the processed first row vector.
Specifically, the first row vector may be smoothed using the following formula:
，
wherein,represents the +.o. for the first OCT image>A smoothed value obtained after smoothing the average value of the pixel values of the column pixels; />A mean value of pixel values representing a j-th column pixel of the first OCT image; k (k) 1 The size of the slide block for the smoothing process is indicated.
For example, in combination with the above example, the smoothed first row vector is expressed asWherein:
. Further, for example, in one embodiment, the first row vector +.>The element with the largest median value is +.>Which is provided withThe corresponding first column coordinate is n.
(3) And calculating the average value of the pixel values of each column of pixels in the second OCT image aiming at the second OCT image to obtain a second row vector formed by the average value of the pixel values of each column of pixels.
Combining the above examples, for example, the second OCT image is noted asThat is, the mean value of the pixel values of each column of pixels in the second OCT image can be calculated using the following formula:
，
wherein,second OCT image +.>An average of pixel values of the column pixels; />Second OCT image +.>Line->Pixel values for column pixels.
In connection with this example, for example, the second row vector is denoted b, In other words, the second row vector includes P elements, the P-th element of which is the average of the pixel values of the P-th column pixels.
(4) And carrying out smoothing processing on the second row vector, and determining a second column coordinate corresponding to the element with the largest median in the processed second row vector.
Specifically, the second row vector may be smoothed using the following formula:
，
wherein,represents the +.o for the second OCT image>A smoothed value obtained after smoothing the average value of the pixel values of the column pixels; b j A mean value of pixel values representing a j-th column pixel of the second OCT image; k (k) 1 The size of the slide block for the smoothing process is indicated.
For example, the smoothed second row vector is expressed as，/>. For example, in one embodiment, the element with the largest median value in the second row vector +.>The corresponding second column coordinate is m.
(5) And when the second column coordinate is smaller than the first column coordinate, determining that the actual size change trend of the target pattern is a smaller trend.
Specifically, the actual size change trend of the target pattern may be determined as follows:
。
S303, searching an actual imaging range type corresponding to the second designated direction and the actual size change trend from the corresponding relation among the predetermined moving direction of the optical path motor, the size change trend of the target pattern and the imaging range type.
It should be noted that, the corresponding relation among the predetermined moving direction of the optical path motor, the size change trend of the target pattern and the imaging range type can be determined by an experimental mode of manually assisting in adjusting the optical path, and in one embodiment of the invention, the target pattern is the outer wall of the catheter:
(1) And controlling the optical path motor to drive the reference arm to move towards the direction of shortening the optical path, and recording the corresponding relation among the size change trend of the target pattern before and after the movement and the type of the imaging range. For example, in one embodiment, experiments prove that when the size variation trend of the target pattern is a trend of increasing, the target pattern is in a normal imaging range, otherwise, in a mirror imaging range;
(2) And controlling the optical path motor to drive the reference arm to move towards the optical path growth direction, and recording the corresponding relation between the size change trend of the target pattern before and after the movement and the imaging range type. In combination with the above example, for example, it is verified through experiments that the size variation trend of the target pattern is a smaller trend, in the normal imaging range, and in the mirror imaging range.
(3) And creating a corresponding relation according to the record. For example, in combination with the above example, the correspondence relationship among the three of the moving direction of the optical path motor, the size variation trend of the target pattern, and the imaging range type is created as shown in table 1:
table 1 correspondence table of moving direction of optical path motor, size change trend of target pattern and imaging range
In combination with table 1, for example, when the optical path motor moves toward the optical path shortening direction in one embodiment, it is determined that the actual size variation trend of the target pattern is a trend of increasing, and at this time, in combination with table 1, it is determined that the actual imaging range type is the normal optical path range, via step S302.
And S304, when the actual imaging range type is a mirror image optical path range, controlling the optical path motor to continuously move a preset distance along a second designated direction so as to enable the reference arm to be transformed from the mirror image optical path position range to a normal optical path range.
When the actual imaging range type is determined to be the mirror image optical path range, at this time, the image currently formed by the OCT apparatus is a mirror image, and thus, when the reference arm is in the mirror image optical path range, first, coarse adjustment is performed so that the reference arm is shifted from the mirror image optical path range to the normal optical path range.
In particular, in coarse adjustment, the movement direction of the reference arm is first determined, and then the reference arm is controlled to move a specified distance in this movement direction. The moving direction is the current second designated direction, and the designated distance is adjusted according to actual needs, which is not limited in this embodiment.
According to the OCT equipment optical path calibration method provided by the embodiment, the optical path motor is controlled to drive the reference arm to move towards the second designated direction, so that the actual size change trend of the target pattern in the second OCT image relative to the target pattern in the first OCT image is determined according to the first OCT image acquired before the optical path motor moves and the second OCT image acquired after the optical path motor moves, and the actual imaging type range corresponding to the second designated direction and the actual size change trend of the target pattern is searched from the predetermined correspondence among the moving direction of the optical path motor, the size change trend of the target pattern and the imaging range type; and when the actual imaging type range is determined to be the mirror image optical path range, controlling the optical path motor to continuously move a preset distance along a second designated direction so as to enable the reference arm to be transformed from the mirror image optical path range to the normal optical path range. Therefore, the aim of rough adjustment can be achieved by heuristically moving the reference arm and collecting the information of the first OCT image and the second OCT image before and after movement, the reference arm can be quickly adjusted to a normal optical path range, and the calibration efficiency is improved.
Fig. 4 is a flowchart of a third embodiment of an optical path calibration method of an OCT apparatus provided in the present application. Referring to fig. 4, the target OCT image is an acquired original OCT image, and the identifying, from the target OCT image, the location information of the outer wall of the catheter includes:
s401, respectively identifying an interference area, an artifact area, a highlight area where the outer wall of the catheter is located and a designated useless area from the target OCT image; the interference area is an area outside the area where the catheter is located in the target OCT image.
It should be noted that image information obtained by catheter scanning is almost completely unpredictable. Therefore, the "image information other than the catheter itself" is regarded as "interference information", and the "region with large amount of interference information" is regarded as "interference region".
Specifically, an image recognition technique may be used to identify, from the target OCT image, an interference region, an artifact region, a highlight region where the outer wall of the catheter is located, and a specified dead region.
Specifically, in one possible implementation, identifying an interference region from the target OCT image includes:
(1) And calculating the accumulated value of the pixel value of each row of pixels in the target OCT image aiming at the target OCT image to obtain a first column vector formed by the accumulated value of the pixel value of each row of pixels.
Specifically, for each row of pixels in the target OCT image, a cumulative sum of pixel values is calculated, resulting in a cumulative sum of pixel values of P-direction pixels, specifically as follows:
，
in the method, in the process of the invention,first ∈h representing target OCT image>The accumulated sum of pixel values of the row of pixels; />First ∈h representing target OCT image>Go->Pixel values for column pixels.
In connection with this example, for example, the first column vector is denoted d,in other words, the first column vector comprises +.>Element of->The individual element is->An accumulated value of pixel values of the row of pixels.
(2) And calculating the mean value and standard deviation of each element in the first column vector, and calculating an interference threshold according to the mean value and the standard deviation.
It should be noted that, for specific implementation principles of calculating the mean value and the standard deviation, reference may be made to the description in the related art, and no further description is given here.
Specifically, the interference threshold may be calculated according to the following formula:
，
wherein d 0 In order for the interference threshold to be a value,representing the mean value of the individual elements in the first column vector,/- >Criteria representing elements in a first column vectorAnd (3) difference.
(3) And for each element in the first column vector, determining a pixel behavior interference area indicated by row coordinates corresponding to the element when the value of the element is larger than the interference threshold value.
For example, d 1 Greater than d 0 At this time, the first row of pixels is determined as an interference area.
In other words, after identification, the identified interference area is as follows:
，
wherein,first ∈h representing target OCT image>The result of the identification of the row of pixels, i.e. +.>Indicate->Row pixel row interference area,>indicate->The row pixels act as non-interfering areas.
For example, fig. 5 is a graph showing the recognition result of the interference area according to an exemplary embodiment of the present application. Referring to fig. 5, a diagram a is a target OCT image, and a diagram B is a corresponding recognition result after recognizing the target OCT image.
Further, in one possible implementation, an artifact region is identified from the target OCT image, where a longitudinal stripe presence region in the image is referred to herein as an "artifact region," including:
(1) For each column of pixels in the target OCT image, searching for a continuous distance of the same pixel value from the column of pixels, and taking the maximum value of the continuous distance as a characteristic value corresponding to the column.
Specifically, the target OCT image is aimed atAnd searching the continuous distance of the same pixel value from the pixels in the column, obtaining the maximum value of the continuous distance, and taking the maximum value as the characteristic value corresponding to the column.
I.e.. The set of characteristic values corresponding to each column is denoted +.>I.e.。
(2) And calculating the mean value and standard deviation of the characteristic values corresponding to each column, and calculating an artifact threshold according to the mean value and the standard deviation.
It should be noted that, for specific implementation principles of calculating the mean value and the standard deviation, reference may be made to the description in the related art, which is not specifically described in this embodiment.
Specifically, the artifact threshold may be calculated as follows:
，
wherein,is an artifact threshold +.>Mean value of characteristic values corresponding to each column, < >>The standard deviation of the feature values corresponding to the respective columns is shown.
(3) And determining the pixel column indicated by each column as an artifact region when the characteristic value is larger than the artifact threshold value according to the characteristic value corresponding to each column.
For example, in one embodiment, the first and second embodiments,is greater than->At this time, the first column of pixels is determined to be an artifact region.
In other words, after identification, the identified artifact region is as follows:
，
in the method, in the process of the invention,first ∈h representing target OCT image>Recognition result of column pixel column, i.e. +. >Indicate->Column pixel columns are artifact regions, < +.>Indicate->The column pixel columns are non-artifact regions.
For example, fig. 6 is a graph showing the result of identifying an artifact region according to an exemplary embodiment of the present application. Referring to fig. 6, a graph a is a target OCT image, and a graph B is a corresponding recognition result after recognizing the target OCT image.
Specifically, in one possible implementation, identifying a specified dead zone from the target OCT image includes:
in the target OCT image, the specified dead zone is relatively fixed, thus targeting the target OCT imageColumn->The corresponding region is regarded as an useless region.
Optionally, identifying a highlight region where the outer wall of the catheter is located from the target OCT image includes:
k-means clustering is carried out on target OCT images (the clustering number K can be set according to the acquisition characteristics of OCT equipment), and further, for each class after aggregation, the area corresponding to the class with the highest pixel average value is regarded as the highlight area where the outer wall of the catheter is located.
And S402, updating the pixel value of each pixel point in the highlight region to 0 when the pixel point belongs to the interference region, the artifact region or the useless region, so as to obtain an updated highlight region.
Assuming that the above identification is performed, the identified areas are respectively: an interference region, an artifact region, a dead region, and a highlight region, and updating a pixel value of each pixel in the highlight region to 0 when the pixel belongs to the interference region, the artifact region, or the dead region, that is:
，
wherein D is i,j A pixel value representing a pixel of an ith column and j rows in the interference area; s is S i,j Pixel values representing the pixels of row j of the ith column in the artifact region; c (C) i,j A pixel value representing a pixel in an ith column j row in the dead zone; h i,j Representing pixel values of the i-th column, j-th row of pixels updated in the highlight region.
S403, calculating the accumulated sum of the pixel values of each column of pixels for the updated highlight region, and obtaining a third row vector formed by the accumulated sum of the pixel values of each column of pixels.
Specifically, the highlight region is first followedAnd accumulating pixel values in the direction to obtain a row vector h. The method comprises the following steps: />
，
Wherein,first ∈of highlighting region>The accumulated sum of the pixel values of the column pixels; />First ∈of highlighting region>Go->Pixel values for column pixels.
For example, fig. 7 is a graph showing the recognition result of a highlight region according to an exemplary embodiment of the present application. Referring to fig. 7, a graph a in fig. 7 is a target OCT image, and a graph B in fig. 7 is a recognition result corresponding to the target OCT image after recognition.
S404, filtering the third row vector, and determining a third column coordinate corresponding to the element with the largest median value in the processed third row vector.
Specifically, in this step, filtering processes such as median filtering and mean filtering may be sequentially performed on the row vector h, where the filtering processes are respectively as follows:
，
wherein,first ∈of highlighting region>Median filtering result values corresponding to the column pixels; media () represents the median value; />A sum of pixel values of a j-th column of pixels representing the highlight region; k (k) 2 Representing the median window size.
，
Wherein,a mean value filtering result value corresponding to the j-th column pixel of the highlight region; />A median filtering result value corresponding to the j-th column pixel of the highlight region; k (k) 3 Representing the mean window size.
For example, the filtered third row vector is expressed as，/>. Further, for example, in one embodiment, the largest element in the third row vector is +.>。
And S405, determining the third column of coordinates as position information of the outer wall of the catheter.
According to the OCT equipment optical path calibration method provided by the embodiment, an interference area, an artifact area, a highlight area where the outside of the catheter is located and a designated useless area are respectively identified from the target OCT image, when each pixel point in the highlight area belongs to the interference area, the artifact area or the useless area, the pixel value of the pixel point is updated to 0, an updated highlight area is obtained, the sum of pixel values of each column of pixels is calculated for the updated highlight area, a third row vector formed by the sum of pixel values of each column of pixels is obtained, filtering processing is carried out on the third row vector, and a third column coordinate corresponding to the element with the largest median value of the processed third row vector is determined, so that the third column coordinate is determined as the position information of the outer wall of the catheter. Thus, the outer wall of the catheter can be accurately identified by eliminating the influence of the interference area, the artifact area and the useless area, and further the optical path calibration is accurately performed based on the outer wall of the catheter.
Corresponding to the foregoing embodiments of an OCT apparatus optical path calibration method, the present application also provides embodiments of an OCT apparatus optical path calibration device.
The embodiment of the optical path calibration device of the OCT device can be applied to the OCT device. The apparatus embodiments may be implemented by software, or may be implemented by hardware or a combination of hardware and software. Taking a software implementation as an example, as a device in a logic sense, the device is formed by reading corresponding computer program instructions in the nonvolatile memory into the memory by the processor of the OCT apparatus in which the device is located. In terms of hardware, as shown in fig. 8, a hardware structure diagram of an OCT apparatus where an optical path calibration device for an OCT apparatus is located in the present application is shown in fig. 8, and in addition to a processor, a memory, a serial port, and a nonvolatile memory shown in fig. 8, the OCT apparatus where the device is located in the embodiment generally includes other hardware according to an actual function of the optical path calibration device for the OCT apparatus, which will not be described herein again.
Fig. 9 is a schematic structural diagram of an embodiment of an optical path calibration device of an OCT apparatus according to the present application. Referring to fig. 9, the apparatus is applied to an OCT apparatus having a catheter connected to the end of a sample arm thereof; the apparatus includes an adjustment module 910, a processing module 920, a determination module 930, and a calibration module 940, where,
The adjusting module 910 is configured to adjust a reference arm of the OCT apparatus to a normal optical path range; wherein when the reference arm is in a normal optical path range, the current image of the OCT apparatus is a positive image;
the processing module 920 is configured to identify, for a currently acquired target OCT image, location information of an outer wall of the catheter;
the determining module 930 is configured to determine a distance to be moved by the reference arm according to the position information and preset position information corresponding to an optical path zero point;
the calibration module 940 is configured to control the optical path motor to drive the reference arm to move the distance towards the first specified direction, so that the outer wall reaches a position corresponding to the preset position information, and the reference arm reaches an optical path zero position.
The apparatus provided in this embodiment may be used to perform the steps of the method embodiment shown in fig. 2, and the specific implementation principle and implementation process may be referred to the description in the foregoing embodiments, which are not repeated herein.
Optionally, the adjusting module 910 is configured to control the optical path motor to drive the reference arm to move toward a second specified direction;
the adjusting module 910 is configured to determine an actual size change trend of the target pattern in the second OCT image relative to the target pattern in the first OCT image according to a first OCT image acquired before the optical path motor moves and a second OCT image acquired after the reference motor moves;
The adjusting module 910 is configured to search an actual imaging range type corresponding to the second specified direction and the actual size change trend from a predetermined correspondence among a moving direction of the optical path motor, a size change trend of the target pattern, and the imaging range type;
the adjusting module 910 is configured to control the optical path motor to continue to move along the second specified direction by a predetermined distance when the actual imaging range type is the mirror image optical path range, so as to change the reference arm from the mirror image optical path bit range to the normal optical path range.
Optionally, the first OCT image and the second OCT image are both acquired original OCT images; the adjusting module 910 is further configured to calculate, for the first OCT image, a mean value of pixel values of each column of pixels in the first OCT image, obtain a first row vector formed by the mean value of pixel values of each column of pixels, perform smoothing processing on the first row vector, and determine a first column coordinate corresponding to an element with a largest median value in the processed first row vector;
the adjusting module 910 is further configured to calculate, for the second OCT image, a mean value of pixel values of each column of pixels in the second OCT image, obtain a second row vector formed by the mean value of pixel values of each column of pixels, perform smoothing processing on the second row vector, and determine a second column coordinate corresponding to an element with a largest median value in the processed second row vector;
The adjusting module 910 is further configured to determine that the actual size change trend of the target image is a trend of increasing when the second column coordinate is greater than the first column coordinate, and determine that the actual size change trend of the target image is a trend of decreasing when the second column coordinate is less than the first column coordinate.
Optionally, the processing module 920 is configured to identify, from the target OCT image, an interference area, an artifact area, a highlight area where an outer wall of the catheter is located, and a specified useless area, respectively; the interference area is an area except the area where the catheter is located in the target OCT image;
the processing module 920 is configured to update, for each pixel in the highlight region, a pixel value of the pixel to 0 when the pixel belongs to the interference region, the artifact region or the useless region, so as to obtain an updated highlight region;
the processing module 920 is configured to calculate, for the updated highlight region, an accumulated sum of pixel values of each column of pixels, obtain a third row vector formed by the accumulated sum of pixel values of each column of pixels, perform filtering processing on the third row vector, and determine a third column coordinate corresponding to an element with a largest median in the processed third row vector;
The processing module 920 is configured to determine the third column coordinate as location information of an outer wall of the catheter.
Optionally, the determining module 930 is configured to determine, according to the position information and the preset position information, a pixel distance to be moved by the reference arm, and determine, according to a predetermined correspondence between the pixel distance and a reference arm movement distance, a distance to be moved by the reference arm corresponding to the pixel distance.
Optionally, the processing module 920 is specifically configured to calculate, for the target OCT image, an accumulated value of pixel values of each row of pixels in the target OCT image, to obtain a first column vector formed by the accumulated value of pixel values of each row of pixels;
the processing module 920 is further configured to calculate a mean value and a standard deviation of each element in the first column vector, and calculate an interference threshold according to the mean value and the standard deviation;
the processing module 920 is further configured to determine, for each element in the first column vector, a pixel behavior interference area indicated by a row coordinate corresponding to the element when the value of the element is greater than the interference threshold.
Optionally, the processing module 920 is specifically configured to, for each column of pixels in the target OCT image, search for a continuous distance of the same pixel value from the column of pixels, and determine a maximum value of the continuous distance as a feature value corresponding to the column;
The processing module 920 is further configured to calculate a mean value and a standard deviation of the feature values corresponding to each column, and calculate an artifact threshold according to the mean value and the standard deviation;
the processing module 920 is further configured to determine, for each column, a pixel column indicated by the column as an artifact region when the feature value is greater than the artifact threshold.
With continued reference to fig. 8, the present application also provides an OCT apparatus, including a memory, a processor, and a computer program stored on the memory and executable on the processor, where the processor implements the steps of the method according to any one of the first aspects of the present application when the processor executes the program.
The present application also provides a storage medium having stored thereon a program which when executed by a processor performs the steps of the method according to any of the first aspects of the present application.
The implementation process of the functions and roles of each unit in the above device is specifically shown in the implementation process of the corresponding steps in the above method, and will not be described herein again.
For the device embodiments, reference is made to the description of the method embodiments for the relevant points, since they essentially correspond to the method embodiments. The apparatus embodiments described above are merely illustrative, wherein the elements illustrated as separate elements may or may not be physically separate, and the elements shown as elements may or may not be physical elements, may be located in one place, or may be distributed over a plurality of network elements. Some or all of the modules may be selected according to actual needs to achieve the purposes of the present application. Those of ordinary skill in the art will understand and implement the present invention without undue burden.
The foregoing description of the preferred embodiments of the present invention is not intended to limit the invention to the precise form disclosed, and any modifications, equivalents, improvements and alternatives falling within the spirit and principles of the present invention are intended to be included within the scope of the present invention.

Claims (9)

1. An OCT apparatus optical path calibration method, characterized in that the method is applied to an OCT apparatus, the end of a sample arm of which is connected to a catheter; the method comprises the following steps:
adjusting a reference arm of the OCT apparatus to a normal optical path range; wherein when the reference arm is in a normal optical path range, the current image of the OCT apparatus is a positive image;
identifying positional information of an outer wall of the catheter for a currently acquired target OCT image;
determining the distance to be moved of the reference arm according to the position information and preset position information corresponding to the optical path zero point;
controlling an optical path motor to drive the reference arm to move towards a first appointed direction by the distance so that the outer wall reaches a position corresponding to the preset position information and the reference arm reaches an optical path zero position;
adjusting a reference arm of the OCT apparatus to a normal optical path range, comprising:
controlling the optical path motor to drive the reference arm to move towards a second designated direction;
Determining the actual size change trend of a target pattern in the second OCT image relative to the target pattern in the first OCT image according to a first OCT image acquired before the optical path motor moves and a second OCT image acquired after the optical path motor moves;
searching an actual imaging range type corresponding to the second designated direction and the actual size change trend from the corresponding relation among the predetermined moving direction of the optical path motor, the size change trend of the target pattern and the imaging range type;
when the actual imaging range type is a mirror image optical path range, controlling the optical path motor to continuously move a preset distance along a second designated direction so as to enable the reference arm to be transformed from the mirror image optical path range to a normal optical path range;
the preset position information corresponding to the optical path zero point refers to position information corresponding to a position where the outer wall of the catheter should be located in the OCT image when the reference arm is located at the optical path zero point position.
2. The method of claim 1, wherein the first OCT image and the second OCT image are both acquired raw OCT images; the determining, according to a first OCT image acquired before the optical path motor moves and a second OCT image acquired after the optical path motor moves, an actual size change trend of the target pattern in the second OCT image relative to the target pattern in the first OCT image, includes:
Calculating the average value of the pixel values of each column of pixels in the first OCT image aiming at the first OCT image to obtain a first row vector formed by the average value of the pixel values of each column of pixels;
smoothing the first row vector, and determining a first column coordinate corresponding to an element with the largest median in the processed first row vector;
calculating the average value of the pixel values of each column of pixels in the second OCT image aiming at the second OCT image to obtain a second row vector formed by the average value of the pixel values of each column of pixels;
smoothing the second row vector, and determining a second column coordinate corresponding to the element with the largest median value in the second row vector after processing;
and when the second column coordinate is smaller than the first column coordinate, determining that the actual size change trend of the target pattern is a smaller trend.
3. The method of claim 1 or 2, wherein the target OCT image is an acquired raw OCT image, the identifying positional information of an outer wall of the catheter comprising:
Respectively identifying an interference area, an artifact area, a highlight area where the outer wall of the catheter is positioned and a designated useless area from the target OCT image; the interference area is an area outside the area where the catheter is located in the target OCT image;
for each pixel point in the highlight region, when the pixel point belongs to the interference region, the artifact region or the useless region, updating the pixel value of the pixel point to 0 to obtain an updated highlight region;
calculating the accumulated sum of the pixel values of each column of pixels for the updated highlight region to obtain a third row vector formed by the accumulated sum of the pixel values of each column of pixels;
filtering the third row vector, and determining a third column coordinate corresponding to the element with the largest median value in the processed third row vector;
and determining the third column of coordinates as position information of the outer wall of the catheter.
4. The method according to claim 1, wherein the determining the distance to be moved by the reference arm according to the position information and the preset position information corresponding to the optical path zero point includes:
determining the pixel distance to be moved of the reference arm according to the position information and the preset position information;
And determining the distance to be moved of the reference arm corresponding to the pixel distance according to the corresponding relation between the predetermined pixel distance and the reference arm movement distance.
5. A method according to claim 3, wherein the identifying of interference regions from the target OCT image comprises:
calculating the accumulated value of the pixel value of each row of pixels in the target OCT image aiming at the target OCT image to obtain a first column vector formed by the accumulated value of the pixel value of each row of pixels;
calculating the mean value and standard deviation of each element in the first column vector, and calculating an interference threshold according to the mean value and the standard deviation;
and for each element in the first column vector, determining a pixel behavior interference area indicated by row coordinates corresponding to the element when the value of the element is larger than the interference threshold value.
6. The method of claim 3, wherein the identifying an artifact region from the target OCT image comprises:
for each column of pixels in the target OCT image, searching for continuous distances with the same pixel value from the column of pixels, and determining the maximum value of the continuous distances as a characteristic value corresponding to the column;
Calculating the mean value and standard deviation of the characteristic values corresponding to each column, and calculating an artifact threshold according to the mean value and the standard deviation;
and determining the pixel column indicated by each column as an artifact region when the characteristic value is larger than the artifact threshold value according to the characteristic value corresponding to each column.
7. An OCT apparatus optical path calibration device, characterized in that the device is applied to an OCT apparatus, the tip of a sample arm of which is connected to a catheter; the device comprises an adjusting module, a processing module, a determining module and a calibrating module, wherein,
the adjusting module is used for adjusting the reference arm of the OCT equipment to a normal optical path range; wherein when the reference arm is in a normal optical path range, the current image of the OCT apparatus is a positive image;
the processing module is used for identifying the position information of the outer wall of the catheter aiming at the currently acquired target OCT image;
the determining module is used for determining the distance to be moved of the reference arm according to the position information and preset position information corresponding to the optical path zero point;
the calibration module is used for controlling the optical path motor to drive the reference arm to move the distance towards a first appointed direction so that the outer wall reaches a position corresponding to the preset position information and the reference arm reaches an optical path zero position;
The adjusting module is used for controlling the optical path motor to drive the reference arm to move towards a second designated direction;
the adjusting module is used for determining the actual size change trend of a target pattern in the second OCT image relative to the target pattern in the first OCT image according to a first OCT image acquired before the optical path motor moves and a second OCT image acquired after the optical path motor moves;
the adjusting module is used for searching an actual imaging range type corresponding to the second designated direction and the actual size change trend from a corresponding relation among a predetermined moving direction of the optical path motor, a size change trend of the target pattern and the imaging range type;
the adjusting module is used for controlling the optical path motor to continuously move a preset distance along a second designated direction when the actual imaging range type is a mirror image optical path range so as to enable the reference arm to be transformed from the mirror image optical path position range to a normal optical path range;
the preset position information corresponding to the optical path zero point refers to position information corresponding to a position where the outer wall of the catheter should be located in the OCT image when the reference arm is located at the optical path zero point position.
8. OCT apparatus, characterized by comprising a memory, a processor and a computer program stored on the memory and executable on the processor, the processor implementing the steps of the method according to any of claims 1-7 when the program is executed.
9. A storage medium having a program stored thereon, which when executed by a processor, implements the steps of the method of any of claims 1-6.
CN202311417334.4A 2023-10-30 2023-10-30 OCT equipment optical path calibration method and device and OCT equipment Active CN117146700B (en)

Priority Applications (1)

Application Number Priority Date Filing Date Title
CN202311417334.4A CN117146700B (en) 2023-10-30 2023-10-30 OCT equipment optical path calibration method and device and OCT equipment

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
CN202311417334.4A CN117146700B (en) 2023-10-30 2023-10-30 OCT equipment optical path calibration method and device and OCT equipment

Publications (2)

Publication Number Publication Date
CN117146700A CN117146700A (en) 2023-12-01
CN117146700B true CN117146700B (en) 2024-01-30

Family

ID=88901130

Family Applications (1)

Application Number Title Priority Date Filing Date
CN202311417334.4A Active CN117146700B (en) 2023-10-30 2023-10-30 OCT equipment optical path calibration method and device and OCT equipment

Country Status (1)

Country Link
CN (1) CN117146700B (en)

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN106691380A (en) * 2016-12-23 2017-05-24 哈尔滨医科大学附属第二医院 OCT probe used for optical path automatic calibration
CN107518877A (en) * 2017-08-25 2017-12-29 广州永士达医疗科技有限责任公司 A kind of calibrating installation and method of OCT conduits
DE17167968T1 (en) * 2016-04-25 2018-01-18 Kabushiki Kaisha Topcon SS-OCT PHASE STABILIZATION WITH REFERENCE SIGNAL CALIBRATION
CN111493831A (en) * 2020-04-24 2020-08-07 天津恒宇医疗科技有限公司 Adaptive calibration system based on OCT light interference and working method
CN111643051A (en) * 2020-06-11 2020-09-11 苏州比格威医疗科技有限公司 Reference arm, ophthalmic OCT imaging system and imaging method thereof
WO2020192699A1 (en) * 2019-03-26 2020-10-01 苏州阿格斯医疗技术有限公司 Mla-oct imaging catheter, mla-oct imaging system and mla-oct imaging method
CN113349737A (en) * 2021-06-30 2021-09-07 深圳英美达医疗技术有限公司 Method for calibrating OCT image of intravascular dual-mode imaging system

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9301687B2 (en) * 2013-03-13 2016-04-05 Volcano Corporation System and method for OCT depth calibration
JP2022154236A (en) * 2021-03-30 2022-10-13 株式会社ニデック Oct apparatus

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE17167968T1 (en) * 2016-04-25 2018-01-18 Kabushiki Kaisha Topcon SS-OCT PHASE STABILIZATION WITH REFERENCE SIGNAL CALIBRATION
CN106691380A (en) * 2016-12-23 2017-05-24 哈尔滨医科大学附属第二医院 OCT probe used for optical path automatic calibration
CN107518877A (en) * 2017-08-25 2017-12-29 广州永士达医疗科技有限责任公司 A kind of calibrating installation and method of OCT conduits
WO2020192699A1 (en) * 2019-03-26 2020-10-01 苏州阿格斯医疗技术有限公司 Mla-oct imaging catheter, mla-oct imaging system and mla-oct imaging method
CN111493831A (en) * 2020-04-24 2020-08-07 天津恒宇医疗科技有限公司 Adaptive calibration system based on OCT light interference and working method
CN111643051A (en) * 2020-06-11 2020-09-11 苏州比格威医疗科技有限公司 Reference arm, ophthalmic OCT imaging system and imaging method thereof
CN113349737A (en) * 2021-06-30 2021-09-07 深圳英美达医疗技术有限公司 Method for calibrating OCT image of intravascular dual-mode imaging system

Also Published As

Publication number Publication date
CN117146700A (en) 2023-12-01

Similar Documents

Publication Publication Date Title
US11913771B2 (en) Information processing device, object measuring system, object measuring method, and program storing medium
JP6230917B2 (en) System and recording medium for needle enhancement in diagnostic ultrasound imaging
US20060239571A1 (en) Method of volume-panorama imaging processing
US20230063939A1 (en) Electro-hydraulic varifocal lens-based method for tracking three-dimensional trajectory of object by using mobile robot
AU2016367430B2 (en) Fast and automated segmentation of layered image with heuristic graph search
US10776937B2 (en) Image processing apparatus and image processing method for setting measuring point to calculate three-dimensional coordinates of subject image with high reliability
JP2008298685A (en) Measuring device and program
KR20140126630A (en) Method for tracking user&#39;s gaze position using mobile terminal and apparatus thereof
Cvišić et al. Recalibrating the KITTI dataset camera setup for improved odometry accuracy
US20140341424A1 (en) Tool tracking during surgical procedures
Jacob et al. Depth information enhancement using block matching and image pyramiding stereo vision enabled RGB-D sensor
JP2006331108A (en) Image processing apparatus, image processing method and program
CN117146700B (en) OCT equipment optical path calibration method and device and OCT equipment
CN114766347A (en) Method for acquiring target three-dimensional position of corn tasseling operation
CN111524188A (en) Lumbar positioning point acquisition method, equipment and medium
KR102532031B1 (en) Crop growth measurement system based on crop images, and method thereof
CN114581678A (en) Automatic tracking and re-identifying method for template feature matching
CN105551042A (en) Determination method and apparatus for mark point positions of scanning bed
JP3505872B2 (en) Moving object tracking device in image
US20230111657A1 (en) Electro-hydraulic varifocal lens-based method for tracking three-dimensional trajectory of moving object
JP4605502B2 (en) Tracking device, tracking method, and biological microscope equipped with the tracking device
JP3524826B2 (en) Three-dimensional image processing method and apparatus, and recording medium storing three-dimensional image processing program
CN113344988B (en) Stereo matching method, terminal and storage medium
CN115280960A (en) Combine harvester steering control method based on field vision SLAM
Wu et al. Fast tracking of catheters in 2D fluoroscopic images using an integrated CPU-GPU framework

Legal Events

Date Code Title Description
PB01 Publication
PB01 Publication
SE01 Entry into force of request for substantive examination
SE01 Entry into force of request for substantive examination
GR01 Patent grant
GR01 Patent grant