KR20170039784A - Optical coherence tomography device for the skin diagnostic - Google Patents

Abstract

The present invention relates to an optical coherence tomography device which measures inner or outer body tissue to diagnose a variety of skin tissue and, more specifically, to a technique capable of visually checking an area in accordance with a size of a lesion of a portion to be photographed. The optical coherence tomography device for skin diagnosis comprises: a guide beam (100) to visually check an area of a diagnosis portion; a diagnosis light source (101) mounted on the guide beam (100) and a 2X1 optical coupler (102) to perform diagnosis; a 2X2 optical coupler (103) to distribute the guide beam and the diagnosis light source to a reference mirror and a sample; a collimation lens (104) and a focusing lens (105) to focus the dispersed guide beam (100) and diagnosis light source (101); the reference mirror (106) to reflect light emitted by the diagnosis light source to be optically analyzed by an optical analyzer; and a hand piece (107) to scan the diagnosis light source and the guide beam of a diagnosis area.

Description

[0001] OPTICAL COHERENCE TOMOGRAPHY DEVICE FOR THE SKIN DIAGNOSTIC [0002]

TECHNICAL FIELD The present invention relates to a coherent tomography apparatus for measuring tissue in the body or in vitro for diagnosis of various skin tissues, and more particularly to a technique for visually confirming a region according to the size of a lesion to be photographed .

Optical coherence tomography (OCT) is a device that uses a coherence length interferometer to image the internal structure of living tissue, which strongly scatter light, at high resolution.

That is, the conventional optical coherence tomography apparatus is roughly divided into a time-domain optical coherence tomography apparatus and a frequency-domain optical coherence tomography apparatus.

First, in the time domain optical coherence tomography system, the reference mirror, which is a basic Michelson interferometer, is moved in the same direction as the optical axis by using PZT or motor, and the optical path difference between the reference mirror and the layer in the target becomes It is a method to acquire the structural information inside the target by obtaining the interference pattern which appears when the coherent length range is satisfied.

On the other hand, the optical coherence tomography system in the frequency domain uses an expensive spectroscope in order to acquire the spectrum according to the wave number through a spectroscope composed of a diffraction grating and obtain the information of the spatial domain by performing Fourier transform on the signal from the Michelson interferometer And the Fourier transform can only use half of the linear detector resolution of the spectroscope. In addition, there is a disadvantage in that the reliability is low due to the acquisition of the structure data of a wrong target due to the distortion of the data due to the sampling of an inappropriate wave number in the Fourier transform.

In order to deepen the high resolution and tissue penetration depth, the laser wavelength used in the time-domain optical coherence tomography apparatus and the frequency-domain optical coherence tomography apparatus uses a laser in the near-infrared region. The wavelength of the region is a wavelength which can not be confirmed by the human eye, so that there is a problem that the region to be diagnosed can not be grasped.

Optical coherence tomography is used in various fields such as ophthalmology, dentistry and dermatology. However, until now, it is mainly used in ophthalmology, and dental and dermatologic uses are limited. Especially, in case of skin diagnosis in dermatology, it is difficult to accurately and precisely diagnose the lesion due to the lack of a method of accurately detecting the diagnosis area of the lesion and using the light source for diagnosis of the non-visible region near infrared ray as described above.

Known prior arts related to the above-mentioned optical coherence tomography apparatuses are disclosed in Japanese Patent Laid-Open Nos. 10-2003-0016584 and 10-2007-0004268.

SUMMARY OF THE INVENTION The present invention has been made in view of the above problems, and it is an object of the present invention to provide an optical coherence tomography apparatus capable of visually confirming a region of a diagnostic region when a diagnostic light source for diagnosis uses a light source other than the visible region. In addition, since the shape of the lesion varies, the display area can be displayed in various forms according to the shape of the lesion.

It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory and are not intended to limit the invention to the particular embodiments that are described. It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory and are not restrictive of the invention, There will be.

In order to accomplish the above object, in the present invention, a guide beam having a wavelength of a visible region capable of confirming a light source and a diagnosis region for diagnosis is used as an area such as a diagnostic region using an optical coupler, The diagnostic beam can be confirmed through the guide beam. And is formed in a guide beam shape of various shapes by a scanner method in order to match shapes with the lesion diagnosis area.

For example, a galvanometer which can be easily controlled can be used as the scanner system.

The optical coherence tomography system for the diagnosis of skin tissue of the present invention can accurately and precisely identify the diagnostic region by the guide beam matching with the diagnostic light source, have.

By implementing the guide beam in various shapes using the scanner method, it is possible to set the diagnosis area optimally for various lesion sizes.

In addition, the optical coherence tomography apparatus for diagnosing skin tissue of the present invention acquires images non-invasively without incision or removal of tissue, and has a high-resolution, real- In addition, since 2D image is obtained in real time, 3D image can be realized in a short time and quantitative information about cell distribution, tumor distribution and lesion stage of skin tissue can be objectified.

1 is a system block diagram of the present invention.

FIG. 1 is a block diagram of a system according to the present invention. Referring to FIG. 1, a guide beam 100 for visually confirming a region of a diagnostic region, a guide beam 100 and a 2X1 optical coupler 102 are used as a light source for diagnosis. 2X2 optical coupler 103 for distributing diagnostic light source 101, guide beam 100 and diagnostic light source 102 to a reference mirror and sample, focusing the scattered guide beam 100 and diagnostic light source 101, A reference mirror 106 for reflecting the light irradiated from the diagnostic light source and performing optical analysis in the optical analyzer 109, a diagnostic light source and a guide for the diagnostic area, And a hand piece 107 for scanning the beam.

100: Guide beam 101: Diagnostic light source
102: 2X1 optical coupler 103: 2X2 optical coupler
104: collimation lens 105: focusing lens
106: reference mirror 107: handpiece
108: Sample 109: Optical analyzer

Claims (6)

The present invention relates to a coherent tomography apparatus for skin diagnosis,
A guide beam (100) for visually confirming a region of a diagnostic region;
A diagnostic light source 101 coupled to the guide beam 100 and the 2X1 optical coupler 102 and used as light for diagnosis;
A 2X1 optical coupler 102 for coupling the guide beam 100 and the diagnostic light source 101;
A 2X2 optocoupler 103 for distributing the guide beam and diagnostic light source to a reference mirror and skin tissue sample or for transferring to a light analyzer 109;
A collimation lens 104 and a focusing lens 105 for focusing the dispersed guide beam 100 and the diagnostic light source 101;
A reference mirror 106 for reflecting the light irradiated from the diagnostic light source and performing optical analysis in the optical analyzer 109;
And a handpiece (107) for scanning the diagnostic light source and the guide beam in the diagnosis area.
The method according to claim 1,
Further comprising a uniaxial galvanometer for vertical axis scanning and horizontal axis scanning of the skin tissue sample along the longitudinal direction of the skin tissue sample.
The method according to claim 1,
Wherein the guide beam has a visible region wavelength of 400 nm to 700 nm.
The method according to claim 1,
Wherein the size of the display area of the guide beam is adjusted to be the same according to the scan size of the diagnostic light source.
5. The method of claim 4,
Wherein the size of the scan area of the guide beam and the diagnostic light source is variable from 1x1 mm to 20x20 mm.
The method according to claim 1,
Wherein the shape of the guide beam of the portion contacting the skin is circular or rectangular so that a scan region can be formed according to the size and shape of various lesions.

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