KR20180076687A - Method of performing oct imaging using a surgical microscope and hybrid beam scanning, and apparatuses for performing the same - Google Patents

Abstract

Disclosed are a method for performing OCT imaging using a surgical microscope and hybrid beam scanning, and apparatuses for performing the same. The method for performing OCT imaging according to an embodiment of the present invention includes the steps of: outputting a dual beam to an observation region of a sample to be observed by the surgical microscope using an optical system of the surgical microscope; and detecting an interference signal based on light scattered from the observation region. A time interval in which the dual beam is emitted to the observation region is different. Accordingly, the present invention can provide a technique for providing 3D blood vessel structure and blood flow information of a surgical operation site.

Description

BACKGROUND OF THE INVENTION 1. Field of the Invention [0001] The present invention relates to a method of performing OCT imaging using an operation microscope and mixed beam scanning, and apparatuses for performing the OCT imaging,

The following embodiments relate to a method of performing OCT imaging using an operation microscope and mixed beam scanning and to devices for performing the same.

An optical photographing apparatus using optical coherence tomography (OCT) is a device capable of photographing an internal image of a subject without incision by a non-contact method. At this time, the optical photographing apparatus can acquire a high-speed three-dimensional image by using the light interference phenomenon.

In addition, the optical photographing apparatus performs blood vessel structure and blood flow test of tissue using OCTA (OCT Angiography). For example, OCTA is a method capable of imaging blood vessel structure and measuring blood flow based on interference signals measured from an optical photographing apparatus.

Since OCTA uses the movement of blood flow (for example, red blood cells) flowing along a blood vessel as a source of an angiographic image signal, it can be applied to blood vessels and blood vessels such as ICG (Indocyanine Green) angiography, Imaging of blood flow information is possible.

Since OCT uses phase to calculate blood flow velocity through analysis of phase information, the range of blood flow velocity measurement is limited to [-π, π], which is a range of phase change amount, and thus there is a limit in that it can only measure blood flow in a narrow velocity range. Since an angle between the imaging beam and the blood flow direction is required in the calculation process, a post-processing process for reconstructing the three-dimensional image of the blood vessel structure is further required. In this process, an error occurs in finding an accurate value. The reliability of the blood flow velocity is lowered.

Embodiments can provide a technique of providing a three-dimensional blood vessel structure and blood flow information of a surgical operation site during an operation using an operation microscope and an OCTA-based optical imaging apparatus.

Embodiments can provide a technique capable of quickly measuring a quantitative velocity of a blood vessel velocity in a wide velocity region using a mixed beam scanning method without calculating a three-dimensional spatial angle of a blood vessel.

According to an embodiment of the present invention, there is provided a method of performing OCT imaging, comprising the steps of: outputting a dual beam to an observation region of a sample to be observed with the surgical microscope using an optical microscope optical system; detecting an interference signal based on light scattered from the observation region; Wherein the double beam has a different time interval to irradiate the observation area.

The outputting may include adjusting a time interval of the double beam by adjusting a scan speed.

The method may further include generating an image of at least one of a blood vessel structure and blood flow of the observation region using the interference signal.

The method may further include acquiring an image corresponding to the observation region through the camera using the optical system of the surgical microscope.

The detecting may include obtaining light scattered in the movement of red blood cells moving along the blood vessel of the observation region, and detecting the interference signal based on the obtained light.

An OCT system according to an embodiment includes an operating microscope for observing a viewing region of a sample and a dual beam connected to the operating microscope and outputting a double beam to the viewing region using an optical system of the operating microscope, And an OCT apparatus for detecting an interference signal based on the light, wherein the double beam differs in time intervals irradiated to the observation region.

The OCT apparatus can adjust the time interval of the double beam by adjusting the scan speed.

The system may further comprise a computer for generating an image of at least one of a blood vessel structure and blood flow of the observation region using the interference signal.

The system may further include a camera for connecting to the surgical microscope and acquiring an image corresponding to the observation area using an optical system of the surgical microscope.

The OCT apparatus may acquire light scattered in the movement of red blood cells moving along a blood vessel of the observation region, and may detect the interference signal based on the obtained light.

The computer can be implemented in the OCT device.

An OCT apparatus according to an embodiment includes a port for connecting to an optical system of a surgical microscope for observing an observation region of a sample, a scanning device for outputting a double beam to the observation region using the optical system of the surgical microscope, And a detector for detecting an interference signal based on light scattered from the observation region, wherein the double beam has a time interval different from that of the irradiation of the observation region.

The scanning device can adjust the time interval of the double beam by adjusting the scan speed.

The detector may acquire light scattered in the movement of red blood cells moving along the blood vessel of the observation region, and may detect the interference signal based on the obtained light.

The OCT apparatus may further include a controller for controlling a position, a scan speed, and an angle of the scanning device.

1 is a schematic block diagram of an OCT system according to one embodiment.
2 is a schematic structural view illustrating the connection structure and operation of the surgical microscope and the OCT apparatus shown in FIG.
Fig. 3 shows examples of lasers of the OCT apparatus shown in Fig.
FIG. 4 shows an example of a mixed beam scanning pattern according to an embodiment.
5A is an embodiment combining an operation microscope and an OCT apparatus.
5B is an example of a cranial window photograph of a mouse brain taken using an operation microscope.
FIG. 5C shows an example of a blood vessel image acquired using the interference signal obtained in the OCT apparatus.
5D shows an example of an image obtained by using a dorsal skinfold window of a mouse with an OCT apparatus.
6 is a flowchart illustrating an operation method of the OCT system shown in FIG.

It is to be understood that the specific structural or functional descriptions of embodiments of the present invention disclosed herein are presented for the purpose of describing embodiments only in accordance with the concepts of the present invention, May be embodied in various forms and are not limited to the embodiments described herein.

Embodiments in accordance with the concepts of the present invention are capable of various modifications and may take various forms, so that the embodiments are illustrated in the drawings and described in detail herein. However, it is not intended to limit the embodiments according to the concepts of the present invention to the specific disclosure forms, but includes changes, equivalents, or alternatives falling within the spirit and scope of the present invention.

The terms first, second, or the like may be used to describe various elements, but the elements should not be limited by the terms. The terms may be named for the purpose of distinguishing one element from another, for example without departing from the scope of the right according to the concept of the present invention, the first element being referred to as the second element, Similarly, the second component may also be referred to as the first component.

It is to be understood that when an element is referred to as being "connected" or "connected" to another element, it may be directly connected or connected to the other element, . On the other hand, when an element is referred to as being "directly connected" or "directly connected" to another element, it should be understood that there are no other elements in between. Expressions that describe the relationship between components, such as "between" and "between" or "neighboring to" and "directly adjacent to" should be interpreted as well.

The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. The singular expressions include plural expressions unless the context clearly dictates otherwise. It will be understood that, in this specification, the terms "comprises ", or" having ", and the like are to be construed as including the presence of stated features, integers, But do not preclude the presence or addition of steps, operations, elements, parts, or combinations thereof.

Unless defined otherwise, all terms used herein, including technical or scientific terms, have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. Terms such as those defined in commonly used dictionaries are to be interpreted as having a meaning consistent with the meaning of the context in the relevant art and, unless explicitly defined herein, are to be interpreted as ideal or overly formal Do not.

Hereinafter, embodiments will be described in detail with reference to the accompanying drawings. However, the scope of the patent application is not limited or limited by these embodiments. Like reference symbols in the drawings denote like elements.

1 is a schematic block diagram of an OCT system according to one embodiment.

1, an OCT system 10 may include a surgical microscope 100, a camera 200, an OCT apparatus 300, and a computer 400. [

The surgical microscope 100 is connected to the camera 200 and the OCT apparatus 300 and the computer 400 is connected to the camera 200 and the OCT apparatus 300. [ Although the computer 400 is illustrated as being implemented within the OCT device 300 in FIG. 1, the present invention is not limited thereto, and the computer 400 may be implemented within the OCT device 300 have.

The surgical microscope 100 can observe the observation region (or the region of interest) of the sample. For example, the sample may comprise a human, patient or animal.

The camera 200 is connected to the surgical microscope 100 and can acquire an image corresponding to an observation region of the sample using an optical system included in the surgical microscope 100. [ The camera 200 may store the acquired image. In addition, the camera 200 may transmit the acquired image to the computer 400.

OCT device 300 is an optical imaging device capable of tomography using light interference phenomenon and can acquire a three-dimensional image at high speed through a mixed beam (e.g., double beam and / or single beam) scanning . In addition, the OCT apparatus 300 can perform OCTA for imaging the blood vessel structure and blood flow based on a signal (for example, an interference signal) obtained through the OCT apparatus 300.

The OCT apparatus 300 is connected to the surgical microscope 100 and can acquire an interference signal for acquiring an image corresponding to an observation region of the sample using an optical system included in the surgical microscope 100. [ The OCT device 300 may transmit an interference signal to the computer 400.

For example, the OCT device 300 acquires light scattered in the movement of red blood cells moving along the blood vessels of the observation region of the sample using the optical system included in the surgical microscope 100, A signal can be detected.

The OCT apparatus 300 can use the mixed beam scanning to quantitatively measure the blood flow velocity in a wide velocity region without the angular information of the blood vessel.

The computer 400 may store the image acquired from the camera 200 and may generate an image for at least one of the vascular structure and blood flow of the observed region of the sample based on the interfering signal transmitted from the OCT device 300 .

At this time, the OCT apparatus 300 can transmit data obtained by performing mixed beam scanning repeatedly at one position of the observation region, that is, interference signals to the computer 400 for imaging (or imaging) the observation region of the sample. In the observation region of the sample, red blood cells can continue to move in blood vessels through which blood normally flows. When the OCT apparatus 300 scans several times at the same position in the observation region of the sample, the phase and amplitude changes may occur in the interference signals detected by the OCT apparatus 300.

The computer 400 may acquire a plurality of images at one position using the repeated interference signals. Thereafter, the computer 400 may compare the differences between the plurality of images. That is, the computer 400 can calculate the blood vessel structure and blood flow information of the observation region of the sample based on the difference.

As described above, the OCT system 10 combines the operation microscope 100 and the OCT apparatus 300 to perform OCT imaging (or imaging) of the observation region (or the region of interest) of the sample observed by the surgical microscope 100 .

The OCT system 10 combines the surgical microscope 100 and the OCT apparatus 300 which are widely used in cerebrovascular surgery and uses the optical system of the surgical microscope 100 to observe the surgical microscope 100. In this case, When the blood vessel structure or blood flow information is required, the OCT apparatus 300 photographs an area such as an observation area of the sample viewed through the surgical microscope 100, and provides the cerebral blood vessel structure and blood flow information of the observation area of the sample in the surgical environment .

When the microvascular morphology and blood flow are required to be examined during surgery in the microvascular surgery, the OCT system 10 provides the cerebral blood vessel structure and blood flow information using the surgical microscope 100 and the OCT apparatus 300 can do.

For example, in the case of a cerebral aneurysm (for example, a cerebral blood vessel wall is weakened and a portion thereof protrudes to form an acute angle, the cerebral blood flow may be blocked by a peripheral blood vessel being compressed by a ruptured or swollen aneurysm) the aneurysm is completely blocked and / or the blood flow is normally maintained in the surrounding blood vessels. In this case, the OCT system (10) ).

In addition, the OCT system 10 can repeatedly observe the blood vessel structure and blood flow in a desired region without injection of contrast agent, such as ICG angiography widely used in clinical practice during surgery.

For example, the OCT system 10 can acquire a cross-sectional image of a tissue 2-3 mm deep from the surface at high image speeds of several hundreds of frames per second or more, enabling fast three-dimensional imaging. This high-speed three-dimensional microimaging can be useful for monitoring the manipulation and manipulation site of a surgical operation. Using the mixed-beam scanning method, the vascular structure and blood flow information based on the difference in signals generated by the movement of red blood cells in the bloodstream It is possible to perform repetitive measurement as much as desired without injecting the contrast agent and the side effects thereof.

FIG. 2 is a schematic structural view illustrating the connection structure and operation of the surgical microscope and the OCT apparatus shown in FIG. 1, and FIG. 3 shows examples of the laser of the OCT apparatus shown in FIG.

1 to 3, the surgical microscope 100 may include an ocular eye piece 110, a port 130, and an optical system 150.

The eyepiece 100 can be displayed (or shown) to a user viewing an observation area of the sample using the optical system 150. [

The port 130 may include a first port 133 and a second port 135. For example, the first port 133 may connect between the surgical microscope 100 and the camera 200, and the second port 135 may connect between the surgical microscope 100 and the OCT device 300.

The camera 200 is connected to the optical system 150, for example, the first optical system 153 via the first port 133 and acquires an image corresponding to the observation region of the sample using the first optical system 153 can do.

The OCT apparatus 300 is connected to the optical system 150, for example, the second optical system 155 through the second port 135 and uses the second optical system 155 to transmit an image corresponding to the observation region of the sample It is possible to obtain an interference signal to be obtained.

That is to say, the camera 200 and the OCT apparatus 300 connected to the surgical microscope 100 use the optical system 150 of the surgical microscope 100 to scan the observation area of the sample in the same area as the field of view of the surgical microscope 100 An image corresponding to the same area can be obtained.

The OCT device 300 includes a port 305, a laser 310, a plurality of spectroscopes 315 and 330, a synchronization device 320, a plurality of circulators 333 and 335, a frequency converter 340, a collimator 345, a reference mirror 347, a scanning device 350, a coupler 360, a detector 370, a DAQ (data acquisition) 380, and a controller controller 390).

The port 305 may connect the OCT device 300 to the optical system 150 of the surgical microscope 100, for example, the second optical system 155.

The laser 310 can output light. For example, the laser 310 may be implemented with a wavelength conversion laser. The laser 310 may include an amplifying medium 310-1 for emitting and amplifying light and a tunable filter 310-3 for converting a pass band according to time .

3, when the laser 310 is implemented as a wavelength conversion laser, the laser 310 may be a fiber-based ring cavity laser structure of (a), a free space ring cavity laser structure of (b) ) Free space linear cavity laser structure. However, the laser 310 is not limited to a wavelength conversion laser, and may be realized by various lasers.

At this time, since the light output from the laser 310 is adjusted in bandwidth, the light irradiated to the sample can be three-dimensionally isotropic. When the light output from the laser 310 is three-dimensionally isotropic, the intensity of the OCT signal, such as the de-correlation, the intensity correlation of the OCT signal, and the speckle variance, Based blood flow velocity measurement, blood flow of the same velocity has the same value regardless of the direction of the flow, and angular information of the blood vessel is not necessary. That is, in performing the operation of converting the interference signal into an image by converting the interference signal into an image, the OCT apparatus 300 does not need the spatial angle information of the blood vessel and does not need to perform complicated post-processing operations.

The first spectroscope 315 can split the light output from the laser 310 into a synchronization beam and a first measurement beam. For example, the synchronization beam may be light that is split into 10% of the light output from the laser 310, and the first measurement beam may be light that is split into 90% of the light output from the laser 310 . The reason why the synchronization beam is spectroscopically separated by 10% output is that the output of the first measurement beam is weakened when it is further spectrally split, and the measurement can not be normally performed because the sample can not be sufficiently transmitted.

The synchronization device 320 may convert a synchronization beam of a predetermined wavelength into a trigger signal. The trigger signal may be a signal for synchronization of the wavelength conversion cycle of light output by the laser 310 and / or the data acquisition period.

The synchronization device 320 may include a fiber bragg grating (FBG) 323 and a trigger circuit 325.

The FBG 323 is a type of optical sensor, and has a periodic microstructure that selectively serves as a mirror to serve as a mirror. Since the FBG 323 has the above-mentioned structure, when light from a certain wide band is scanned on the FBG 323, only light with a narrow spectral width is reflected back to the grating. In doing so, the FBG 323 serves to reflect a predetermined wavelength of the synchronization beam.

The trigger circuit 325 can convert the light reflected from the FBG 323 into a trigger signal.

The second spectrometer 330 may be capable of spectroscopically dividing the first measurement beam into a reference beam and a second measurement beam. For example, the reference beam may be light that is spectrally split at a 10% output of the first measurement beam, and the second measurement light 40 may be light that is spectrally split at 90% of the first measurement beam.

The frequency converter 340 may convert the frequency of the reference beam. Through the frequency conversion, all the frequency values have a value larger than 0, and the measurable range in the depth direction of the sample can be widened.

The reference mirror 347 can reflect the reference beam having the changed frequency and transmit it to the coupler 360.

The scanning device 350 may perform a mixed beam (e.g., dual beam and / or single beam) scanning using a second measurement beam. For example, the scanning device 350 may split the second measurement beam into a first side beam and a second side beam, irradiate the sample with spatial spacing, and return the reflected first and second side beams together.

The scanning device 350 may include a collimator 351, a free space frequency shifter 353, a first lens 355, a second lens 357, and a beam scanner 359 have.

The free space frequency converter 353 may generate a dual beam, e.g., a first side beam and a second side beam, using the second measurement beam. In addition, the free space frequency converter 353 may combine the first side beam and the second side beam, reflected from the sample, into one beam.

The first lens 355 adjusts the angle of the first side beam and the second side beam in parallel with each other and the second lens 357 adjusts the angle of the light passing through the first lens 355 to be incident on one point have.

The beam scanner 359 can adjust the angle of the first side beam and the second side beam incident on the point through the second lens 357 to enter the surface of the observation region of the sample. For example, the beam scanner 359 may be a galvanometer mirror scanner. At this time, the first side beam and the second side beam may have a constant spatial interval from each other. Further, the first side beam and the second side beam may be different in the time interval irradiated to the observation region of the sample.

In the measuring method using the beam scanner 359, the first side beam is irradiated to the surface of the observation region of the sample, the second side beam is irradiated to the same position after a predetermined time, And the surface of the observation region of the sample is measured.

The measurement method using the beam scanner 359 may include a first measurement operation, a second measurement operation, a third measurement operation, and a fourth measurement operation. The first measurement operation, the second measurement operation, the third measurement operation, and the fourth measurement operation will be described by way of example.

For convenience of explanation, one direction of the surface of the observation region of the sample is set as the X direction, and the direction perpendicular to the X direction is set as the Y direction. The time at which the first side beam and the second side beam are irradiated from one end to the other end in the X direction on the same Y position through the adjustment of the angle of the beam scanner 359 is referred to as a scan time S, (G) is a time difference in which the second side beam is irradiated to the same position where the first side beam is measured after being irradiated to a predetermined position of the observation region of the first side beam. The first side beam and the second side beam are irradiated with a constant spatial interval, which is caused by the spatial spacing of the first side beam and the second side beam. The time interval G is affected by the scan time S. As the scan time S is increased, the time interval G is decreased. As the scan time S is slower, the time interval G is increased do.

In the first measurement operation, the first side beam and the second side beam can be irradiated and reflected at a predetermined time interval from one end of the X-direction to the other end of the surface of the observation region of the sample through the movement of the beam scanner 359 .

In the second measurement operation, the first measurement operation is repeated a predetermined number of times, and the time interval at which the first side beam and the second side beam are irradiated can be adjusted by changing the scan speed of the beam scanner 359 have. As described above, by adjusting the scan time S, the time interval G can be adjusted.

The scan speed of the beam scanner 359 is fixed in the third measurement operation after the second measurement operation is completed and the first side beam and the second side beam are moved from one end of the surface of the measurement object O in the X direction to the other end It can be repeatedly irradiated and reflected a predetermined number of times.

The third measurement operation may be an operation performed to have a wide range with a larger time interval (G). If the first side beam and the second side beam are repeatedly irradiated as many times as necessary, a wide range of blood flow velocities can be obtained.

The fourth measurement operation is an operation of repeating the first measurement operation to the third measurement operation by moving the measurement position in the Y direction after the third measurement operation is completed. The fourth measuring operation can be repeatedly performed from one end to the other end in the Y direction until completion.

A phase value for a two-dimensional image of the surface of the observation region of the sample can be obtained through the first measurement operation to the fourth measurement operation.

The control of the position of the beam scanner 359 and the scanning speed S and the selective control of only one of the first side beam and the second side beam in the first measuring operation to the fourth measuring operation is carried out through control of a preprogrammed electrical signal Lt; / RTI > Changing the scanning type to match the biological characteristics of the sample can adjust the range of the measurable blood flow velocity, which can be very easy to apply and versatile.

The controller 390 can control the operation of the scanning device 350. In addition, the controller 390 can control the operation of the scanning device 350 in response to a signal input from the user through the computer 400. [

For example, the controller 390 may adjust the angle, scan rate, and position (e.g., depth direction y) of the beam scanner 359.

The coupler 360 can generate an interference signal by combining the scattered (or reflected) light transmitted from the observation region of the sample and the light reflected and transmitted from the reference mirror 337. For example, the coupler 360 can use the light scattered (or reflected) from the observation region of the sample and the light reflected and transmitted from the reference mirror 337 to the same degree (for example, 50:50) have.

The detector 370 can detect an interference signal (or interference information) of light. For example, the detector 370 may convert the interference signal into a digital signal.

The DAQ 380 may record (or collect) a digital signal in response to the trigger signal.

The computer 400 may acquire an image through image processing of the digital signal recorded in the DAQ 380. [

FIG. 4 shows an example of a mixed beam scanning pattern according to an embodiment.

Referring to FIG. 4, the OCT apparatus 300 repeatedly photographs a cross-sectional image at the same position using mixed beam scanning, for example, dual beam scanning, and measures a phase change with time, ) Can be obtained.

For convenience of explanation, the depth direction of the sample is defined as z, the direction in which high-speed scanning is performed is defined as x, the direction of low-speed scanning is defined as y, and the time taken to acquire a single sectional image is defined as T.

Since the double beam scans along the same path at regularly spaced intervals, the time interval between the two beams can be changed according to the scan speed in the x direction. As shown in FIG. 4, when the time interval between the double beams is T / 32, the scanning intervals are increased to 2T, 4T and 8T, and the time intervals of the two beams are T / 16, T / It is possible to implement various time intervals shorter than the conventional period T such as 4.

On the other hand, since a relatively long time interval is required to measure a very slow blood flow velocity such as a capillary blood vessel, after the double beam scanning is completed, a scanning pattern having a predetermined period T is repeatedly inputted several times, Slow blood flow velocity measurements may be possible by implementing large time intervals.

The time interval that can be implemented in Fig. 4 has a time interval in a wide region from T / 32 to 8T. In FIG. 4, it takes a total of 38T to perform the x scan, and the y scan is performed in the form of a step function in which the y direction scan does not operate during 38T and is located at the same position and moves to the next position after passing 38T. FIG. 4 is an example of a mixed beam scanning pattern implementation, and it is possible to determine the measurable blood flow velocity range by changing the scanning mode as necessary.

5B is an example of a cranial window photograph of a mouse brain photographed using an operation microscope, and FIG. 5C is a view showing a blood vessel image obtained by using an interference signal obtained from an OCT apparatus, FIG. 5D shows an example of an image obtained by using a dorsal skinfold window of a mouse with an OCT apparatus.

Figures 5B and 5C show images for the same observation area of the sample, i.e. the mouse brain. The cranial window image of the mouse brain photographed using the surgical microscope 100 is shown in FIG. 5B, and the angiography of the mouse brain generated using the interference signal acquired by the OCT apparatus 300 is shown in FIG. 5C . The larger the blood flow, the more red blood cells tend to move faster, so that the amplitude and phase changes of the interference signal acquired by the OCT device 300 can be large. Accordingly, the blood vessel image corresponding to the blood vessel generated through the computer 400 can be seen well.

5D is an image of a mouse's dorsal skinfold window taken with OCT. Although not a cerebral angiogram, there are many blood vessels in the dorsal window, which is a popular model for acquiring OCT vascular images. The blood vessel image obtained by the mixed beam scanning method is the image showing only the blood vessel structure on the left side and the image providing the blood flow velocity information on the right side. By implementing various time intervals, it is possible to image blood flow with various speeds, and it is possible to provide information on blood vessels such as arteries and veins by the difference in speed.

6 is a flowchart illustrating an operation method of the OCT system shown in FIG.

Referring to FIG. 6, the OCT apparatus 300 may output a dual beam to an observation region of a sample observed by the surgical microscope 100 using the optical system 150 of the surgical microscope 100 (S610).

The OCT apparatus 300 can detect the interference signal based on the light scattered (or reflected) from the observation region of the sample (S630).

The computer 400 may generate an image for at least one of the vascular structure and the blood flow of the observation region of the sample based on the interference signal (S650).

When the blood vessel structure and blood flow information are required for confirming the success of cerebral blood vessel surgery, the OCT system 10 combines the OCT apparatus 300 based on the OCTA, which does not need to use the contrast microscope 100, and the contrast microscope 100 (Or imaging) the blood vessel structure and blood flow information of the observation region of the sample, which is seen as the surgical microscope 100, irrespective of the side effect of the contrast agent and the time limit.

The apparatus described above may be implemented as a hardware component, a software component, and / or a combination of hardware components and software components. For example, the apparatus and components described in the embodiments may be implemented within a computer system, such as, for example, a processor, a controller, an arithmetic logic unit (ALU), a digital signal processor, a microcomputer, a field programmable gate array (FPGA) , A programmable logic unit (PLU), a microprocessor, or any other device capable of executing and responding to instructions. The processing device may execute an operating system (OS) and one or more software applications running on the operating system. The processing device may also access, store, manipulate, process, and generate data in response to execution of the software. For ease of understanding, the processing apparatus may be described as being used singly, but those skilled in the art will recognize that the processing apparatus may have a plurality of processing elements and / As shown in FIG. For example, the processing unit may comprise a plurality of processors or one processor and one controller. Other processing configurations are also possible, such as a parallel processor.

The software may include a computer program, code, instructions, or a combination of one or more of the foregoing, and may be configured to configure the processing device to operate as desired or to process it collectively or collectively Device can be commanded. The software and / or data may be in the form of any type of machine, component, physical device, virtual equipment, computer storage media, or device , Or may be permanently or temporarily embodied in a transmitted signal wave. The software may be distributed over a networked computer system and stored or executed in a distributed manner. The software and data may be stored on one or more computer readable recording media.

The method according to an embodiment may be implemented in the form of a program command that can be executed through various computer means and recorded in a computer-readable medium. The computer-readable medium may include program instructions, data files, data structures, and the like, alone or in combination. The program instructions to be recorded on the medium may be those specially designed and configured for the embodiments or may be available to those skilled in the art of computer software. Examples of computer-readable media include magnetic media such as hard disks, floppy disks and magnetic tape; optical media such as CD-ROMs and DVDs; magnetic media such as floppy disks; Magneto-optical media, and hardware devices specifically configured to store and execute program instructions such as ROM, RAM, flash memory, and the like. Examples of program instructions include machine language code such as those produced by a compiler, as well as high-level language code that can be executed by a computer using an interpreter or the like. The hardware devices described above may be configured to operate as one or more software modules to perform the operations of the embodiments, and vice versa.

While the present invention has been particularly shown and described with reference to exemplary embodiments thereof, it is to be understood that the invention is not limited to the disclosed exemplary embodiments. For example, it is to be understood that the techniques described may be performed in a different order than the described methods, and / or that components of the described systems, structures, devices, circuits, Lt; / RTI > or equivalents, even if it is replaced or replaced.

Therefore, other implementations, other embodiments, and equivalents to the claims are also within the scope of the following claims.

Claims (15)

Outputting a double beam to an observation region of a sample to be observed with the surgical microscope using an optical system of an operation microscope;
Detecting an interference signal based on light scattered from the observation region
Lt; / RTI >
Wherein the double beam has a different time interval to irradiate the observation region.
The method according to claim 1,
Wherein the outputting step comprises:
Adjusting a time interval of the double beam by adjusting a scan speed
Gt; OCT < / RTI >
The method according to claim 1,
Generating an image for at least one of a blood vessel structure and a blood flow of the observation region using the interference signal
Further comprising the steps of:
The method according to claim 1,
Acquiring an image corresponding to the observation region through a camera using the optical system of the surgical microscope
Further comprising the steps of:
The method according to claim 1,
Wherein the detecting comprises:
Acquiring light scattered in movement of red blood cells moving along a blood vessel of the observation region, and detecting the interference signal based on the obtained light
Gt; OCT < / RTI >
A surgical microscope for observing the observation region of the sample; And
An OCT apparatus connected to the surgical microscope and outputting a double beam to the observation region using an optical system of the surgical microscope and detecting an interference signal based on light scattered from the observation region;
Lt; / RTI >
Wherein the double beam has a different time interval to irradiate the observation region.
The method according to claim 6,
The OCT apparatus includes:
The OCT system adjusts the time interval of the double beam by adjusting the scan speed.
The method according to claim 6,
A computer for generating an image of at least one of a blood vessel structure and a blood flow of the observation region using the interference signal;
And an OCT system.
The method according to claim 6,
A camera for connecting to the surgical microscope and acquiring an image corresponding to the observation area using an optical system of the surgical microscope;
And an OCT system.
The method according to claim 6,
The OCT apparatus includes:
Acquiring light scattered in movement of red blood cells moving along a blood vessel of the observation region, and detecting the interference signal based on the obtained light.
The method according to claim 6,
Wherein the computer is implemented within the OCT device.
A port for connecting to an optical system of a surgical microscope for observing a viewing region of the sample;
A scanning device for outputting a double beam to the observation region using an optical system of the surgical microscope; And
And a detector for detecting an interference signal based on light scattered from the observation region
Lt; / RTI >
Wherein the double beam has a different time interval to irradiate the observation region.
13. The method of claim 12,
The scanning device includes:
And adjusting a time interval of the double beam by adjusting a scan speed.
13. The method of claim 12,
The detector comprises:
Acquiring light scattered in movement of red blood cells moving along a blood vessel of the observation region, and detecting the interference signal based on the obtained light.
13. The method of claim 12,
A controller for controlling the position, scan speed, and angle of the scanning device,
Further comprising an OCT device.

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