KR101033516B1 - Photometric Application Oral Cancer Early Diagnosis System and Method - Google Patents

Abstract

The present invention is an optical measuring method that inserts an optical sensor into the oral cavity of a patient and irradiates and detects light of an Xe lamp or LED lamp by using a property of oral cancer cells, which is a kind of protein that is difficult to visually observe, at first, by absorbing and emitting light energy. By the non-invasive, non-incision diagnostic method for oral cancer early diagnosis system and method for the early diagnosis. According to an aspect of the present invention, a medical diagnostic system includes a lamp for emitting light using an inert gas, an optical focusing module for focusing and delivering light emitted from the lamp, and radiating the light to the body to be diagnosed. An optical fiber sensor for detecting light emitted from the body part to be diagnosed, a spectroscope for spectroscopically detecting the light detected by the optical fiber sensor into a plurality of lights, and a light for generating a corresponding electrical signal for each of the light spectroscopically detected by the spectroscope Sensing means.

Oral Cancer, Early Diagnosis, Xe / LED Lamps, Auxiliaries, Spectroscopes, Photomultipliers

Description

Optical Measurement Application Early Diagnosis System and Method

The present invention relates to an early diagnosis system for oral cancer, and a method thereof. In particular, an oral cancer cell, which is a kind of protein that is difficult to visually observe initially, absorbs and emits light energy. The present invention relates to an early oral cancer diagnosis system and a method for early diagnosis of oral cancer by a non-invasive and non-incision diagnostic method by an optical measurement method for irradiating and detecting light of a lamp or an LED lamp.

Conventionally, a patient with vitiligo in the cheek mucosa, the mucosa of the mouth, the lips, the tongue, the teeth, the palate, the mouth, and the mouth is used for the early diagnosis of cancer. Was removed and observed under a microscope to determine whether cancer cells. This technique was burdensome to cut the patient's skin and had to wait 1-2 weeks for the test results.

In addition, the laser was mainly used as a light source when measuring light applications. Lasers have good monochromaticity, but are difficult to handle and expensive, making these shortcomings a significant obstacle for commercialization in optical application diagnostic systems. Even in the early diagnosis system of oral cancer, 337 nm of 315 nm, 337 nm, and 357 nm, which are fixed output wavelengths of the nitrogen (N ₂ ) laser, was mainly used. Today, a dye laser that can vary in wavelength from ultraviolet to infrared is used. Also used. In addition, a diode laser having a wavelength of 405 nm or the like may be used. However, using such a laser is difficult to commercialize a low price.

In addition, although conventionally used an ICCD (Intensified Charge Coupled Device) camera as a means of amplifying and reading a very weak spectrum signal obtained from the light measurement, ICCD camera is also expensive and has become a significant obstacle to low-cost commercialization.

In addition, since the fluorescence signal emitted from the skin tissue is not measured when the skin in the oral cavity and the optical fiber sensor directly contact each other, it is necessary not only to properly maintain the distance between the optical fiber sensor and the skin, but also to detect the optimal fluorescence according to the progress of cancer cells. Auxiliary tools to match distances are also needed.

The present invention is to solve the above problems, an object of the present invention is to replace the expensive laser light source with Xe lamp or LED lamp to diagnose oral cancer early by non-invasive, non-incision diagnostic method by optical measurement method It uses a lower cost photomultiplier tube instead of an ICCD camera, and utilizes an assistive tool that allows the optical sensor to be inserted into the patient's mouth to be adjusted to the proper distance from the skin. An oral cancer early diagnosis system and method for detecting a fluorescence signal are provided.

First, to summarize the features of the present invention, in accordance with an aspect of the present invention for achieving the above object, the medical diagnostic system, a lamp for emitting light using an inert gas; An optical focusing module for focusing and transferring the light emitted from the lamp; An optical fiber sensor for irradiating the transmitted light to a body part to be diagnosed and detecting light emitted from the body part to be diagnosed; A spectroscope for spectroscopy the light detected by the optical fiber sensor into a plurality of lights; And light sensing means for generating a corresponding electrical signal for each of the light spectroscopy in the spectrometer.

Xe is included as the inert gas.

The light focusing module may include: a band pass filter configured to filter light emitted from the lamp; A lens for focusing light passing through the band pass filter; And a fiber-optic probe for receiving light passing through the lens.

In addition, the medical diagnostic system according to another aspect of the present invention, the lamp for emitting light using the LED; A lens for focusing light from the lamp; A fiber-optic probe for receiving and passing light passing through the lens; An optical fiber sensor for irradiating the transmitted light to a body part to be diagnosed and detecting light emitted from the body part to be diagnosed; A spectroscope for spectroscopy the light detected by the optical fiber sensor into a plurality of lights; And light sensing means for generating a corresponding electrical signal for each of the light spectroscopy in the spectrometer.

Characterized in that for the diagnosis of oral diseases, wherein the body part to be diagnosed as the skin tissue in the oral cavity.

The light sensing means may include an ICCD camera or a photomultiplier tube.

The spectrometer may spectroscopically generate 3 to 5 lights having different wavelengths, and may convert each of the 3 to 5 lights into an electrical signal using 3 to 5 sets of photomultiplier tubes as the light sensing means.

The optical fiber sensor may include an excitation light source fiber for transmitting the transmitted light; A fluorescence detection fiber around the excitation light source fiber for detecting light emitted from the body part to be diagnosed; Fixing means for wrapping and fixing the excitation light source fiber and the fluorescence detection fiber; spring; And an insertion tube which protrudes in one direction of the fixing means and wraps the end of the excitation light source fiber and the fluorescence detection fiber that penetrates the spring, and uses the elastic force of the spring to make the excitation light source fiber and the An end of the fluorescence detection fiber may move left and right within the insertion tube.

The optical fiber sensor may include an excitation light source fiber for transmitting the transmitted light; A fluorescence detection fiber around the excitation light source fiber for detecting light emitted from the body part to be diagnosed; Fixing means for wrapping and fixing the excitation light source fiber and the fluorescence detection fiber; And an insertion tube for inserting and wrapping the ends of the excitation light source fiber and the fluorescence detection fiber protruding in one direction of the fixing means, and corresponding excitation of the excitation light source fiber and the fluorescence detection fiber inserted into the insertion tube. The end portion of the excitation light source fiber and the fluorescence detection fiber is inserted into the insertion tube by using a frictional force assisting means requiring a constant force between the surface of the coating portion and a corresponding inner portion of the insertion tube. You can move from side to side.

The spectrometer reflects incident light at a first mirror, diffracts light reflected at the first mirror at a diffraction grating, and continuously reflects diffracted light emitted at the diffraction grating at a second mirror and a third mirror. It is possible to output the spectroscopic lights coming out of the plurality of slits.

The medical diagnosis system may further include analyzing means for calculating light intensity data for each wavelength from the electrical signal and calculating a pattern value for a body part to be diagnosed based on the light intensity data for each wavelength.

The analyzing means may include: an intensity analyzer which analyzes the electrical signal to calculate light intensity data for each wavelength; A peak value obtaining unit for finding one lowest point value corresponding to an inflection point and two peak values in the light intensity data for each wavelength and outputting corresponding light intensity values; And calculating a first ratio of a first peak value of the peak values to the lowest point value and a second ratio of a second peak value of the peak values to the lowest point value, and again a first ratio to a second ratio. It may include a pattern value calculation unit for calculating the ratio comparison value of the ratio as the pattern value.

In addition, the medical diagnostic method according to another aspect of the present invention, the step of emitting light through a lamp using an inert gas; Focusing the emitted light and transferring the emitted light to an optical fiber; Irradiating the light transmitted to the optical fiber to a body part to be diagnosed and detecting light emitted from the body part to be diagnosed; Spectroscopy the detected light into a plurality of lights; And generating a corresponding electrical signal for each of the spectroscopic lights.

And, the medical diagnostic method according to another aspect of the present invention, the step of emitting light using the LED; Transferring the emitted light to an optical fiber; Irradiating light transmitted to the optical fiber to a body part to be diagnosed and detecting light emitted from the body part to be diagnosed; Spectroscopy the detected light into a plurality of lights; And generating a corresponding electrical signal for each of the spectroscopic lights.

After generating the electrical signal, the method further includes calculating light intensity data for each wavelength from the electrical signal and calculating a pattern value for the body part to be diagnosed based on the light intensity data for each wavelength.

The calculating of the pattern value may include: calculating light intensity data for each wavelength by analyzing the electrical signal; Finding one lowest point value and two peak values corresponding to an inflection point in the light intensity data for each wavelength and outputting corresponding light intensity values; And calculating a first ratio of a first peak value of the peak values to the lowest point value and a second ratio of a second peak value of the peak values to the lowest point value, and again a first ratio to a second ratio. Calculating a ratio comparison value of the ratio as the pattern value.

As described above, according to the oral cancer early diagnosis system and method according to the present invention, it is possible to increase the value of low-cost commercialization by replacing the existing expensive laser light source with Xe lamp or LED lamp when oral cancer diagnosis.

In addition, according to the oral cancer early diagnosis system and method according to the present invention, up to 3 to 5 fluorescence wavelengths at the same time using up to 3 to 5 photomultiplier tube instead of the conventional ICCD camera for fluorescence detection for oral cancer diagnosis It can be detected and analyzed to diagnose oral cancer cells.

And, according to the oral cancer early diagnosis system and method according to the present invention, the distance between the optical fiber sensor cross-section and cancer cells can be properly adjusted by using an auxiliary tool, the maximum fluorescence intensity according to the progress of the oral cancer cells in the oral cavity Can be measured.

In order to fully understand the present invention, the operational advantages of the present invention, and the objects achieved by the practice of the present invention, reference should be made to the accompanying drawings which illustrate preferred embodiments of the present invention and the contents described in the accompanying drawings.

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

1 is a view for explaining the oral cancer early diagnosis system 100 according to an embodiment of the present invention. Referring to Figure 1, oral cancer early diagnosis system 100 according to an embodiment of the present invention Xe lamp 101, light focusing module 110, excitation light source fiber 115, fluorescence detection fiber 116, light A fiber sensor 120, a spectrometer 130, a photomultiplier tube 140, and a computer 150.

The oral cancer early diagnosis system 100 is for diagnosing oral related diseases in which the body to be diagnosed is a skin tissue in the oral cavity, but is not limited thereto. Non-invasive or non-incision is performed by optical measurement using the above components. As a diagnostic method, it can be used as a medical diagnostic system for the early diagnosis of various parts of the body to be diagnosed, such as surgically or medically damaged skin tissue.

Xe lamp 101 is a light irradiation means for emitting light using a low-cost material containing an inert gas such as Xe. The wavelength of the light irradiated from the Xe lamp 101 may vary depending on the content of the Xe gas filled in the container, but the wavelength of light required for the body part to be diagnosed, for example, about 250-800 nm for oral diagnosis. Proper light with spectral wavelengths can be generated.

The light focusing module 110 focuses the light emitted from the Xe lamp 101 and transmits the light to the optical fiber, that is, the excitation light source fiber 115, the band pass filter 111, the lens 112, and the fiber- And an optical probe 113. The band pass filter (BPF) 111 may filter the incident light emitted from the Xe lamp 101 to pass only the spectral wavelengths of light required for the body part to be diagnosed, for example, 250 to 800 nm. have. The lens 112 may focus light passing through the band pass filter 111 to be collected in a width of 10 to 15 nm. The fiber optic probe 113 receives the light passing through the lens 112 and transmits the light to the excitation light source fiber 115.

As described above, since the spectral wavelength of the light generated from the Xe lamp 101 may be distributed over 250 to 800 nm, a band pass filter 111 at the rear end of the Xe lamp 101 may be installed to diagnose oral cancer as shown in [Table 1]. It can be derived so that the wavelength range of the required light source is 280 ~ 450nm and the half width of the light source is 10 ~ 15nm by the lens 112.

Compared with the case of using a laser as a light source, the half width of the light source is a little wider, but there is no problem as a light source for diagnosing body tissues such as oral cancer. As a result, an expensive laser can be replaced by a technology using an inexpensive Xe lamp, so that it can be developed into a technology that can be commercialized and distributed in a practical manner. As shown in [Table 1], the emission wavelengths that can be detected from the tissues with reference to the excitation wavelengths applied to medical diagnosis such as oral cancer are shown as reference. Such emission wavelength can be observed using a photomultiplier tube or an ICCD camera as described below.

TABLE 1

Oral Cancer Marker Excitation wavelength (nm) Emission wavelength (nm) NADH 290, 340 440, 450 FAD 450 515 Collagen cross-links 325 400 Elastin cross-links 325 400 Collagen powder 280, 265, 330, 450 310, 385, 390, 530 Elastin powder 350, 410, 450 310, 385, 390, 530

On the other hand, the light collected by the lens 112 and then delivered to the fiber-optic probe 113 may be transmitted to the optical fiber sensor 120 connected through the excitation light source fiber 115, the optical fiber sensor 120 Fluorescence emitted from a body to be diagnosed through the oral cavity may be detected through the fluorescence detection fiber 116 disposed in a plurality of circles around the central excitation light source fiber 115. For example, the light emitted from the excitation light source fiber 115 of the optical fiber sensor 120 is irradiated to a portion of the oral cavity suspected to be cancer cells, and thus the fluorescence emitted from the cancer cells is circular to the outside of the center of the optical fiber sensor 120. It can be detected through the fluorescence detection fiber 116 is arranged in plurality.

The spectrometer 130 decomposes the light detected by the optical fiber sensor 120 into a plurality of lights. The photomultiplier tube 140 may multiply photoelectrons for each of the light spectroscopy 130 and generate a corresponding amplified corresponding electrical signal by the multiplied photons. The structure of using 3 to 5 sets of photomultiplier tubes for processing the 3 to 5 light having different wavelengths from the spectrometer 130 at the photomultiplier tube 140 will be described in more detail with reference to FIG. 4. .

Here, a structure using the photomultiplier tube 140 having three sets will be described, but the present invention is not limited thereto, and as many sets of photomultiplier tubes as possible can be used, the photomultiplier tube 140 can be used. You can also use an expensive Charge Coupled Device (ICCD) camera instead of the expensive one. Although the ICCD camera is conventionally used as a means of amplifying and reading the spectral signal for the entire wavelength after the wavelength decomposition through the spectroscope 130 for the very weak light obtained from the optical fiber sensor 120, the ICCD camera is expensive and commercialized at low cost. Has been a significant obstacle. ICCD cameras are commonly used as a means of observing multiple fluorescence wavelengths simultaneously in optical application measurements. On the other hand, the photomultiplier tube 140 can be measured separately for each wavelength. On the other hand, in order to diagnose oral cancer, it should be able to detect up to three to five wavelengths at the same time to help determine whether oral cancer cells. Therefore, ICCD cameras can be used to measure multi-wavelength fluorescence, but they are very expensive and can be an obstacle to realistic marketability. Alternatively, it is possible to replace the expensive ICCD by mounting three photomultiplier tubes 140 at the end of the spectrometer 130 to set the fluorescence wavelength to be measured respectively.

The spectral signal amplified by the photomultiplier tube 140 with respect to the fluorescence detected by the optical fiber sensor 120 may be finally delivered to the computer 150. Accordingly, the computer 150 may receive software such as a predetermined application program or the like. The hardware can be operated to diagnose / analyze information on oral cancer cells.

2 is a view for explaining the optical fiber sensor 120 and the auxiliary tool according to an embodiment of the present invention. 2, in addition to the excitation light source fiber 115 and the fluorescence detection fiber 116, the optical fiber sensor 120 according to an embodiment of the present invention, the fixing means 121, the spring 122, and the insertion Tube 123.

The light focused at the lens 112 and then transmitted to the fiber-optic probe 113 is incident and transmitted to the excitation light source 115 at the center of the single or plural fibers to be irradiated to the body part to be diagnosed, such as tissue in the oral cavity. Can be. Although the excitation light source fiber 115 is illustrated as a single fiber in the drawing, this is only one example, and the excitation light source fiber 115 may be configured in the form of three bundles, for example. After the light is irradiated to the body part to be diagnosed by the excitation light source fiber 115, the fluorescence detection fiber 116 circularly disposed in a plurality (for example, in the form of a bundle of three) around the central excitation light source 115. ) Detects light emitted from the body part of the diagnosis.

The fixing means 121 is a means for wrapping and fixing the excitation light source fiber 115 and the fluorescence detection fiber 116, and a spring 122 is inserted between the fixing means 121 and the insertion tube 123 serving as an auxiliary means. . The excitation light source fiber 115 and the fluorescence detection fiber 116 protrude in one direction of the fixing means 121 and penetrate the spring 122, and the excitation light source fiber 115 and the fluorescence detection fiber ( The end of the 116 is inserted so that the insertion tube 123 surrounds a portion including the end thereof. The ends of the excitation light source fiber 115 and the fluorescence detection fiber 116 can move left and right inside the insertion tube 123 by using the elastic force of the spring 122.

For example, in order to efficiently detect fluorescence, it is necessary to adjust the interval between the ends of the excitation light source fiber 115 and the fluorescence detection fiber 116 and the body part to be diagnosed such as oral cancer cells according to the progress of the cells. . Therefore, as shown in FIG. 2, the spring 122 is manufactured to be adjusted while pressing with an appropriate force of 1 to 10 mm.

In addition, as shown in FIG. 3, the excitation light source fiber 115 and the fluorescence detection fiber 116 protruding in one direction of the fixing means 121 for wrapping and fixing the excitation light source fiber 115 and the fluorescence detection fiber 116 are inserted. The portion that can be inserted into the tube 123 may be covered with a predetermined material. A certain force must be applied to the surface 124 of the covered portion or the corresponding inner portion of the insertion tube 123 so that it can slide over the friction between them. For example, by properly selecting the type of coating or material in the form of embossing, frictional forces are generated on the surface 124 than otherwise, so that the insertion tube 123 or the coated fiber does not slide easily but slides with a slight force. You can move it from side to side.

In the case of the fixed type without using the spring as shown in Figure 3, it can be manufactured to move by 0.5%, 1%, .. of the entire moving range each time a small force is applied by hand, or 0.5mm, 1mm ,. It is also possible to produce such that the movement by a certain distance.

By using the auxiliary means as shown in Fig. 2 or 3, after inserting the optical fiber sensor 120 in the oral cavity, it is possible to detect the maximum fluorescence signal by maintaining an appropriate distance from the sensor and the skin of the cancer cells in the oral cavity Can help Insertion tube 123, which is an auxiliary means as described above, can be manufactured to be detachable from the excitation light source fiber 115 and the fluorescence detection fiber 116 in a form of a hole, and by adjusting the pressing force appropriately during diagnosis Freely adjust the distance to the skin tissue.

4 is a view for explaining the spectrometer 130 and the photomultiplier tube 140 according to an embodiment of the present invention. Referring to FIG. 4, the spectrometer 130 may include three mirrors 131, 133, and 134 and one diffraction grating 132. The photomultiplier tube 140 includes three sets of photomultiplier tubes 141 to 143.

Light transmitted from the fluorescence detection fiber 116 of the optical fiber sensor 120 and incident through the slit of the spectrometer 130 is reflected by the first mirror 131, and the light reflected by the first mirror 131 is Diffracted at the diffraction grating 132 to be spectroscopically diffracted or diffracted light emitted from the diffraction grating 132 is continuously reflected at the second mirror 133 and the third mirror 134 and through three slits Each of the spectroscopic lights can be output. For more spectral numbers, each of the spectroscopic lights may be output in 4, 5, ... slits. If each of the spectroscopic lights is output through 4, 5, ... slits, a corresponding number of sets of photomultipliers will also be required.

As described above, in the present invention, for medical diagnosis such as oral cancer, the light is emitted using an inert gas such as Xe, and then focused with an optical fiber, and the light focused with the optical fiber is irradiated to a body part to be diagnosed. The light emitted from the body part to be diagnosed is detected. The light thus detected is spectroscopic in a plurality of lights (for example, three wavelengths), and an electrical signal corresponding to the corresponding multiplied photoelectron by photomultiplying using the photomultiplier tube 140 for each of the spectroscopic lights. (Amplified spectral signal result) can be obtained. Spectral signal results by the photomultiplier tube 140 may be analyzed in the computer 150 to obtain a diagnosis result for oral cancer factors as shown in Table 1.

5 is a view for explaining the oral cancer early diagnosis system 200 according to another embodiment of the present invention. Referring to FIG. 5, the oral cancer early diagnosis system 200 according to another embodiment of the present invention includes an LED lamp 201, a focusing lens 202, a fiber-optic probe 203, an excitation light source fiber 115, and a fluorescent light. The detection fiber 116, the optical fiber sensor 120, the spectrometer 130, the photomultiplier tube 140, and the computer 150 are included.

The oral cancer early diagnosis system 200 of FIG. 5 is configured to replace the Xe lamp 101 and the light focusing module 110 with the LED lamp 201, the focusing lens 202, and the fiber-optic probe 203 in FIG. 1. As such, the remaining components operate similarly to FIG. 1.

Oral cancer early diagnosis system 200 of FIG. 5 is also intended for the diagnosis of oral-related diseases in which the body part to be diagnosed as the oral skin tissue, but is not limited thereto, by using an optical measurement method using the above components. Invasive and non-incision diagnostic methods can be used as a medical diagnostic system for early diagnosis of various parts of the body to be diagnosed, such as surgically or medically damaged skin tissue.

The LED lamp 201 is light irradiation means for emitting light using a low cost material such as a light emission diode (LED). The wavelength of the light irradiated from the LED lamp 201 may vary depending on the characteristics of the semiconductor compound to be PN-bonded when the LED is manufactured. For this purpose, it is possible to select and apply an appropriate LED among each LED emitting various wavelengths in the range of about 200 ~ 500nm.

The focusing lens 202 focuses the light from the LED lamp 201 and delivers it to the fiber optic probe 203, and the fiber-optic probe 203 transmits the light passing through the lens 202. It receives and transmits the excitation light source fiber (115).

As above, by selecting the appropriate LED to be used in the LED lamp 201 can be selectively applied between the spectral wavelength of the light source between 200 ~ 500nm, as shown in Table 1 is also suitable for the 280 ~ 450nm wavelength band that is required for oral cancer diagnosis The LED can be sufficiently realized by the selection of the LED, and the light generated from the LED lamp 201 can be properly focused by the focusing lens 202 to be led to the optical fiber.

In this case, the half width of the light source may be slightly wider than that of using the laser as a light source (for example, about 15 nm), but there is no problem as a light source for diagnosing body tissues such as oral cancer. As a result, the expensive laser can be replaced by a technology using a low-cost LED, so that it can be developed into a technology that can be commercialized and distributed in a practical manner.

Meanwhile, the fiber-optic probe 203 transmits the light emitted from the LED lamp 201 to the optical fiber, that is, the excitation light source fiber 115, and the light transmitted to the fiber-optic probe 203 is again an excitation light source. The optical fiber sensor 120 may be transmitted to the optical fiber sensor 120 connected through the fiber 115, and a plurality of circularly arranged fluorescent detection fibers 116 may be disposed around the central excitation light source fiber 115 constituting the optical fiber sensor 120. Fluorescence emitted from the body to be diagnosed, such as the oral cavity, can be detected. For example, the light emitted from the excitation light source fiber 115 of the optical fiber sensor 120 is irradiated to a portion of the oral cavity suspected to be cancer cells, and thus the fluorescence emitted from the cancer cells is circular to the outside of the center of the optical fiber sensor 120. It can be detected through the fluorescence detection fiber 116 is arranged in plurality.

The spectrometer 130 decomposes the light detected by the optical fiber sensor 120 into a plurality of lights. The photomultiplier tube 140 may multiply photoelectrons for each of the light spectroscopy 130 and generate a corresponding amplified corresponding electrical signal by the multiplied photons. Their structure using 3 to 5 sets of photomultiplier tubes for processing the 3 to 5 light having different wavelengths from the spectrometer 130 at the photomultiplier tube 140 has already been described.

Although the structure using the photomultiplier tube 140 having three sets is described here, the present invention is not limited thereto, and the number of photomultiplier tubes corresponding to the number of spectroscopic lights can be used, and the photomultiplier tube 140 can be used. You can also use an expensive Charge Coupled Device (ICCD) camera instead of the expensive one. Although the ICCD camera was used as a means of amplifying and reading the spectral signal for the entire wavelength after the wavelength decomposition through the spectroscope 130 for the very weak light obtained from the optical fiber sensor 120, the ICCD camera is expensive and is quite expensive for commercialization. It has been an obstacle. ICCD cameras are commonly used as a means of observing multiple fluorescence wavelengths simultaneously in optical application measurements. On the other hand, the photomultiplier tube 140 can be measured separately for each wavelength. On the other hand, in order to diagnose oral cancer, it is necessary to be able to detect up to three to five wavelengths at the same time to help determine whether oral cancer cells. Therefore, ICCD cameras can be used to measure multi-wavelength fluorescence, but they are very expensive and can be an obstacle to realistic marketability. Alternatively, it is possible to replace the expensive ICCD by mounting three photomultiplier tubes 140 at the end of the spectrometer 130 to set the fluorescence wavelength to be measured respectively.

The spectral signal amplified by the photomultiplier tube 140 with respect to the fluorescence detected by the optical fiber sensor 120 may be finally delivered to the computer 150. Accordingly, the computer 150 may receive software such as a predetermined application program or the like. The hardware can be operated to diagnose / analyze information on oral cancer cells.

Here, as shown in FIG. 2, in addition to the excitation light source fiber 115 and the fluorescence detection fiber 116, an optical fiber sensor 120 including a fixing means 121, a spring 122, and an insertion tube 123 is used. do.

As described above, in the present invention, for medical diagnosis such as oral cancer, the light is emitted using the Xe lamp 101 or the LED lamp 201 and transmitted to the optical fiber, and the light transmitted to the optical fiber is transmitted to the body to be diagnosed. Irradiation to the site detects light emitted from the part of the body to be diagnosed. The light thus detected is spectroscopic in a plurality of lights (for example, three wavelengths), and an electrical signal corresponding to the corresponding multiplied photoelectron by photomultiplying using the photomultiplier tube 140 for each of the spectroscopic lights. (Amplified spectral signal result) can be obtained. Spectral signal results by the photomultiplier tube 140 may be analyzed in the computer 150 to obtain a diagnosis result for oral cancer factors as shown in Table 1.

For example, as shown in FIG. 6, while adjusting the distance D between the end of the excitation light source fiber 115 and the fluorescence detection fiber 116 and a sample site such as a corresponding oral cancer cell, the light detected by the fluorescence detection fiber 116 is adjusted. Results of the computer 150 analysis of the spectral signal results are shown in FIGS. 7 and 8. The predetermined analysis system of the computer 150 may collect and analyze spectral signals output from the photomultiplier tube 140 to calculate light intensity data as shown in FIGS. 7 and 8.

7 is a graph of the detected light intensity by distance (D) between the tip of the fiber and the sample site for normal skin.

As shown in FIG. 7, a similar signal intensity and a pattern are shown at a distance between D = 0 mm and D = 1 mm, which are in a perfect contact state, and there is a difference in overall signal intensity between 2.5 to 10 mm, but the signal type shows similar results.

FIG. 8 is a graph showing the detected light intensity by distance (D) between the tip of the fiber and the sample site for dysplastic skin in the precancerous stage.

As shown in Figure 8, Figure 2 also shows a similar signal intensity and pattern at a distance of D = 0mm and D = 1mm in a fully contact state, and there is a difference in signal strength between 2.5 ~ 10mm, but the signal type has similar results Indicated.

The overall result shows that there is almost no difference in signal pattern between normal and abnormal in the case of full contact and very short distance within D = 1mm. Even when the distance is about 10mm, the difference in the signal pattern between normal abnormal is not large. Turned out to be. Therefore, in the cross-sectional structure of the optical fiber sensor 120, since the excitation light source fiber 115 for emitting excitation light is located at the center, and the fluorescence detection fiber 116 for collecting the generated fluorescence signal is distributed around it. Too close or too far from the contact surface may result in a failure to sufficiently reflect the spontaneous fluorescence signal of the biological tissue generated by the excitation light, so it seems that a proper distance is required.

As described above, by collecting and analyzing the spectral signal output from the photomultiplier tube 140 to calculate the light intensity data, it is possible to generate a graph as shown in Figs. 7 and 8, but to the light intensity data on such a graph There is an unclear way to make a diagnosis on whether a sample site is normal only by relying on it intuitively.

Therefore, the detection light analysis system 900 as shown in FIG. 9, which can quantify the pattern of the sample region from the above characteristics on the graph, may be provided in the computer 150 to increase the accuracy and clarity of the diagnosis. The detection light analysis system 900 may not be mounted on the computer 150 or may operate as an independent dedicated device.

As illustrated in FIG. 9, the detection light analysis system 900 may include an intensity analyzer 910, a peak value acquirer 920, and a pattern value calculator 930.

The intensity analyzer 910 collects and analyzes a spectral signal output from the photomultiplier tube 140 to calculate light intensity data for each wavelength as shown in FIGS. 7 and 8. When detecting the fluorescence emitted from the sample portion through the fluorescence detection fiber 116, the intensity analysis unit 910 normalizes the calculated light intensity data for each wavelength because the measurement environment may be slightly different from measurement to measurement. Normalized light intensity data may be generated. For example, with respect to wavelength-specific light intensity data as shown in FIG. 7 or 8, the maximum light intensity value may be replaced with 1.0, and the remaining light intensity values may be replaced with relative values thereof.

The peak value acquisition unit 920 includes one lowest value corresponding to an inflection point (for example, an optical intensity value of a wavelength of 420 nm) and a peak value in the light intensity data for each wavelength as shown in FIG. 7 or 8. ) 2 (eg, light intensity values of wavelength 390 and 470 nm) are found and the corresponding light intensity values are output. In this case, the peak value acquisition unit 920 performs distortion correction so that the values of the inflection point and the values in the vicinity of the inflection point are smoothly fluctuated and not fluctuated in order to facilitate the acquisition of the lowest and peak values as described above. In order to find an inflection point, a minimum function and peak values as described above may be obtained by deriving a predetermined function of light intensity data for each wavelength as shown in FIG. 7 or 8 and obtaining a solution for the inflection point of the function. .

The pattern value calculating unit 930 calculates a pattern value from one of the lowest point values (for example, the light intensity value of wavelength 420 nm) and two peak values (for example, the light intensity values of wavelength 390 and 470 nm). do. For example, the pattern value calculator 930 may include a first ratio of two peak values (for example, a light intensity value having a wavelength of 390 nm) and two peak values for the lowest point value among two peak values for the lowest point value. The second ratio of the second peak value (for example, the light intensity value of wavelength 470 nm) is calculated, and the ratio comparison value (for example, the first ratio / second ratio of the first ratio to the second ratio) is calculated again. ) Can be calculated as the pattern value. Such a pattern value may be displayed through a predetermined display means.

For example, in the D = 2.5mm example of FIG. 7 (in the case of normal skin), the pattern value as above may be about 0.42, and in the D = 2.5mm example of FIG. 8 (in the case of dysplastic skin in the precancerous stage), the pattern The value may be about 0.87. As such, as the development from normal to early cancer increases the pattern value as above, by presenting such a pattern value as well as an intuitive and qualitative graph, the accuracy and clarity of diagnosis can be improved.

As described above, optimal embodiments have been disclosed in the drawings and the specification. Although specific terms have been used herein, they are used only for the purpose of describing the present invention and are not intended to limit the scope of the invention as defined in the claims or the claims. Therefore, those skilled in the art will understand that various modifications and equivalent other embodiments are possible from this. Therefore, the true technical protection scope of the present invention will be defined by the technical spirit of the appended claims.

1 is a view for explaining an oral cancer early diagnosis system according to an embodiment of the present invention.

2 is a view for explaining an optical fiber sensor and the auxiliary tool according to an embodiment of the present invention.

3 is a view for explaining an optical fiber sensor and an auxiliary tool according to another embodiment of the present invention.

4 is a view for explaining a spectroscope and a photomultiplier tube according to an embodiment of the present invention.

5 is a view for explaining an oral cancer early diagnosis system according to another embodiment of the present invention.

6 is a view for explaining the distance between the end of the fiber and the sample site in the auxiliary tool according to an embodiment of the present invention.

7 is a graph of the detected light intensity by distance between the tip of the fiber and the sample site for normal skin.

8 is a graph of the detected light intensity by distance between the tip of the fiber and the sample site for dysplastic skin.

9 is a block diagram of a detection light analysis system according to an embodiment of the present invention.

Claims (16)

A lamp that emits light using an inert gas; An optical focusing module for focusing and transferring the light emitted from the lamp; An optical fiber sensor including an excitation light source fiber in the center for radiating the transmitted light to a body part to be diagnosed, and a fluorescence detection fiber around the excitation light source fiber for detecting light emitted from the body part to be diagnosed; A spectroscope for spectroscopy the light detected by the optical fiber sensor into a plurality of lights having different wavelengths; And Optical sensing means for generating a corresponding electrical signal for each of the light spectroscopy in the spectrometer, An end of the fluorescence detection fiber through an auxiliary means coupled to the optical fiber sensor such that an end of the excitation light source fiber and the fluorescence detection fiber is moved within the means surrounding the end of the excitation light source fiber and the fluorescence detection fiber Medical diagnostic system, characterized in that the interval between the body parts of the diagnosis is controlled. The method of claim 1, And Xe as the inert gas. The optical focus module of claim 1, A band pass filter for filtering light emitted from the lamp; A lens for focusing light passing through the band pass filter; And Fiber-optic probe for receiving light passing through the lens Medical diagnostic system comprising a. A lamp for emitting light using the LED; A lens for focusing light from the lamp; A fiber-optic probe for receiving and passing light passing through the lens; An optical fiber sensor including an excitation light source fiber in the center for radiating the transmitted light to a body part to be diagnosed, and a fluorescence detection fiber around the excitation light source fiber for detecting light emitted from the body part to be diagnosed; A spectroscope for spectroscopy the light detected by the optical fiber sensor into a plurality of lights having different wavelengths; And Optical sensing means for generating a corresponding electrical signal for each of the light spectroscopy in the spectrometer, The excitation light source fiber and the fluorescence through an auxiliary means coupled to the optical fiber sensor to move the ends of the excitation light source fiber and the fluorescence detection fiber inside the means surrounding the ends of the excitation light source fiber and the fluorescence detection fiber. Medical diagnostic system, characterized in that the interval between the end of the detection fiber and the body part to be diagnosed is adjusted. The medical diagnostic system according to claim 1 or 4, wherein the medical diagnosis system is for diagnosing oral diseases related to the body part to be diagnosed as oral skin tissue. The method according to claim 1 or 4, wherein the light sensing means, A medical diagnostic system comprising an ICCD camera or a photomultiplier tube. The method according to claim 1 or 4, The spectrometer is spectroscopic 3 to 5 light of different wavelengths, And each of the three to five lights is converted into an electrical signal by using three to five sets of photomultipliers as the light sensing means. The optical fiber sensor according to claim 1 or 4, Fixing means for wrapping and fixing the excitation light source fiber and the fluorescence detection fiber; spring; And an insertion tube for inserting and wrapping the ends of the excitation light source fiber and the fluorescence detection fiber which protrude in one direction of the fixing means and penetrate the spring. And an end of the excitation light source fiber and the fluorescence detection fiber move left and right inside the insertion tube by using an elastic force of the spring. The optical fiber sensor according to claim 1 or 4, Fixing means for wrapping and fixing the excitation light source fiber and the fluorescence detection fiber; And an insertion tube for inserting and wrapping the ends of the excitation light source fiber and the fluorescence detection fiber protruding in one direction of the fixing means. Corresponding portions of the excitation light source fiber and the fluorescence detection fiber inserted into the insertion tube are coated, The end of the excitation light source fiber and the fluorescence detection fiber is moved left and right inside the insertion tube by using a frictional force assisting means requiring a constant force between the surface of the coated portion and the corresponding inner portion of the insertion tube. Medical diagnosis system. The spectrometer according to claim 1 or 4, wherein Reflect incident light at the first mirror, Diffracted light reflected from the first mirror in a diffraction grating, And reflect the diffracted light emitted from the diffraction grating in the second mirror and the third mirror in succession to output the spectroscopic lights exiting the plurality of slits. The method according to claim 1 or 4, And analyzing means for calculating light intensity data for each wavelength from the electrical signal and calculating a pattern value for the body part to be diagnosed based on the light intensity data for each wavelength. The method of claim 11, wherein the analysis means, An intensity analyzer for analyzing the electrical signal to calculate light intensity data for each wavelength; A peak value obtaining unit for finding one lowest point value corresponding to an inflection point and two peak values in the light intensity data for each wavelength and outputting corresponding light intensity values; And Calculate a first ratio of a first peak value among the peak values to the lowest value and a second ratio of a second peak value among the peak values relative to the lowest point value; A pattern value calculation unit that calculates a ratio comparison value of 1 ratio as the pattern value. Medical diagnostic system comprising a. Emitting light through a lamp using an inert gas; Focusing the emitted light and transferring the emitted light to an optical fiber sensor; Irradiating the light transmitted using the optical fiber sensor to a body part to be diagnosed and detecting light emitted from the body part to be diagnosed; Spectroscopy the detected light into a plurality of lights having different wavelengths; And Generating a corresponding electrical signal for each of the spectroscopic lights, The optical fiber sensor irradiates the light transmitted using the excitation light source fiber at the center to the diagnosis target body part, and detects the light emitted from the body part to be diagnosed using the fluorescence detection fiber around the excitation light source fiber, The excitation light source fiber and the fluorescence through an auxiliary means coupled to the optical fiber sensor to move the ends of the excitation light source fiber and the fluorescence detection fiber inside the means surrounding the ends of the excitation light source fiber and the fluorescence detection fiber. A method of operating a medical diagnosis system, characterized in that the distance between the end of the detection fiber and the body part to be diagnosed is adjusted. Emitting light using the LED; Transferring the emitted light to an optical fiber sensor; Irradiating the light transmitted using the optical fiber sensor to a body part to be diagnosed and detecting light emitted from the body part to be diagnosed; Spectroscopy the detected light into a plurality of lights having different wavelengths; And Generating a corresponding electrical signal for each of the spectroscopic lights, The optical fiber sensor irradiates the light transmitted using the excitation light source fiber at the center to the diagnosis target body part, and detects the light emitted from the body part to be diagnosed using the fluorescence detection fiber around the excitation light source fiber, The excitation light source fiber and the fluorescence through an auxiliary means coupled to the optical fiber sensor to move the ends of the excitation light source fiber and the fluorescence detection fiber inside the means surrounding the ends of the excitation light source fiber and the fluorescence detection fiber. A method of operating a medical diagnosis system, characterized in that the distance between the end of the detection fiber and the body part to be diagnosed is adjusted. 15. The method of claim 13 or 14, wherein after generating the electrical signal: Calculating light intensity data for each wavelength from the electrical signal and calculating a pattern value for a body part to be diagnosed based on the light intensity data for each wavelength; Method of operation of the medical diagnostic system further comprising. The method of claim 15, wherein the calculating of the pattern value comprises: Analyzing the electrical signal to calculate light intensity data for each wavelength; Finding one lowest point value and two peak values corresponding to an inflection point in the light intensity data for each wavelength and outputting corresponding light intensity values; And Calculate a first ratio of a first peak value among the peak values to the lowest value and a second ratio of a second peak value among the peak values relative to the lowest point value; Calculating a ratio comparison value of one ratio as the pattern value Method of operation of a medical diagnostic system comprising a.

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