Breast cancer diagnosis system

Abstract

The present invention relates to a breast cancer diagnosis system. The breast cancer diagnosis system may include: a probe that sequentially outputs light of multiple wavelengths in the near-infrared region toward a target object, receives reflected light from the target object, and sequentially processes the reflected light; a central control device that controls the operation of the probe, receives optical data of the reflected light detected by the probe, calculates the chromophore concentration of the target object for each chromophore based on the optical data, and generates a chromophore image representing the concentration distribution of each chromophore; and a display that outputs the image generated by the central control device. The probe may include N (N is a natural number greater than or equal to 1) channel signal processing units, each including at least one light irradiation module and at least one light collection module. Each of the channel signal processing units may operate sequentially to generate the optical data of the reflected light.

Description

Technical Field

[0001] The present invention relates to a breast cancer diagnosis system, and more particularly, to a breast cancer diagnosis system that utilizes near-infrared measurement technology to diagnose breast cancer. Background Art

[0002] Early diagnosis and treatment of diseases are very important for a healthy life. Among many diseases, cancer is a serious life-threatening disease, and early diagnosis and treatment of cancer are receiving more and more attention.

[0003] On the other hand, for women, breast cancer has the highest incidence rate among breast cancer, thyroid cancer, stomach cancer, colorectal cancer, lung cancer, etc. Therefore, in order to effectively treat breast cancer, the development of a method that can effectively diagnose breast cancer in its early stages has become a focus of attention.

[0004] Mammography is a well-known existing technology for diagnosing breast cancer. It uses X-rays to detect lesions inside the breast. However, because the difference in X-ray absorption between breast tissue and cancer is very small, screening for cancer in breast tissue is difficult.

[0005] As a method to solve the above problem, there is a method of diagnosing breast cancer using diffuse optical tomography, which uses the wavelength of light to obtain a two-dimensional or three-dimensional image of the internal tissue of the breast.

[0006] For example, Korean Patent Publication No. 10-2019-0048249 discloses an apparatus and method for diagnosing breast cancer using diffuse optical tomography.

[0007] Specifically, Korean Patent Publication No. 10-2019-0048249 discloses a device that diagnoses breast cancer by converting an optical signal and an infrared signal detected using the optical signal and irradiating the diagnosis object into digital signals, respectively, and calculating the signal size difference and phase difference of each converted digital signal. Summary of the Invention

[0008] Technical issues

[0009] An object of the present invention is to provide a breast cancer diagnosis system that utilizes multiple wavelengths of light in the near-infrared region (DMW-NIRS, Discrete Multi Wavelength Near Infra-Red Spectroscopy) to diagnose breast cancer, thereby enabling more convenient imaging and accurate diagnosis of breast cancer.

[0010] The objects of the present invention are not limited to the above objects, and those skilled in the art can more clearly understand other objects not mentioned through the following description.

[0011] Technical Solution

[0012] As a technical solution for achieving the above-mentioned technical objectives, a breast cancer diagnosis system according to one embodiment of the present invention utilizes near-infrared measurement technology. The breast cancer diagnosis system may include: a probe for sequentially outputting light of multiple wavelengths in the near-infrared region toward a target object, receiving and sequentially processing reflected light from the target object; a central control device for controlling the operation of the probe, receiving optical data of the reflected light detected by the probe, calculating the chromophore concentration of the target object for each chromophore based on the optical data, and generating a chromophore image representing the concentration distribution of each chromophore; and a display for outputting the image generated by the central control device. The probe may include N (N is a natural number greater than or equal to 1) channel signal processing units, each comprising at least one light irradiation module and at least one light collection module. Each of the channel signal processing units may operate sequentially to generate the optical data of the reflected light.

[0013] Furthermore, the probe may include: a main body, including a plurality of the channel signal processing units, a first control unit and a first communication unit, the first control unit controlling the operation of the channel signal processing units, and the first communication unit transmitting output data of the first control unit to the outside; and a contact surface, arranged on the lower surface of the main body, the light irradiation module and the light collection module of the channel signal processing unit may be arranged to be exposed to the outside through an opening formed on the contact surface, the N channel signal processing units may be arranged in a horizontal direction along one axis of the probe, the plurality of light irradiation modules and the plurality of light collection modules of the channel signal processing units adjacent to each other may be arranged adjacent to each other, the plurality of light irradiation modules may be arranged in a row side by side with the one axis, the plurality of light collection modules and the plurality of light irradiation modules may be separated by a specified distance and arranged in a row side by side with the one axis.

[0014] Furthermore, each of the above-mentioned channel signal processing units may respectively include: at least one of the above-mentioned light irradiation modules, which are arranged adjacent to each other; the above-mentioned light collection module, which is arranged at a specified distance from the above-mentioned light irradiation module; and a driving chip, which sequentially outputs a driving signal for driving the above-mentioned light irradiation module according to the control signal of the above-mentioned first control unit, and transmits the above-mentioned light data of the above-mentioned reflected light detected by the above-mentioned light collection module to the above-mentioned first control unit. The above-mentioned driving chip of each of the above-mentioned channel signal processing units can sequentially output 4 to 12 driving signals so that the above-mentioned light irradiation module sequentially outputs 4 to 12 beams of light with different wavelengths.

[0015] Furthermore, the first control unit may include: a first decoder for sequentially transmitting control signals for operating the driving chips of each of the channel signal processing units; and a second decoder for sequentially receiving and outputting the light data of the reflected light output by each of the driving chips.

[0016] In addition, the above-mentioned probe may also include a flashing light emitting diode (LED) or a liquid crystal display in the shell of the above-mentioned body. As the above-mentioned first control unit receives all the above-mentioned light data of the above-mentioned reflected light corresponding to the unit scan through each of the above-mentioned channel signal processing units, the above-mentioned flashing light emitting diode or the above-mentioned liquid crystal display may indicate that the unit scan has been completed.

[0017] Furthermore, the central control device may calculate the chromophore concentration of the target object by inputting the measured values ​​of each wavelength of the reflected light detected by the probe into a learning model, and the learning model performs machine learning based on training data in which the measured values ​​of each wavelength of light are matched one-to-one with the concentrations of a plurality of chromophore substances.

[0018] In addition, the above-mentioned central control device can sequentially receive the unit scan data transmitted from each of the above-mentioned channel signal processing units, import each of the above-mentioned unit scan data into the above-mentioned learning model to calculate the above-mentioned chromophore concentration, and generate a unit frame image by respectively representing the above-mentioned chromophore concentration on a two-dimensional coordinate system. The above-mentioned unit scan data can include the above-mentioned light data of the above-mentioned reflected light reflected based on the above-mentioned light of more than 4 and less than 12 different wavelengths output by the above-mentioned light irradiation module of each of the above-mentioned channel signal processing units, and the data of the blank space between each coordinate can represent the value calculated by the difference algorithm.

[0019] In addition, the above-mentioned central control device can output a diagnosis interface for guiding the scanning steps through the above-mentioned probe. The above-mentioned diagnosis interface can include a shooting guidance interface that displays the left chest area and the right chest area respectively. The first area of ​​interest interface and the second area of ​​interest interface can be displayed in the above-mentioned shooting guidance interface. The first area of ​​interest interface is used to display the shooting area that needs to be diagnosed, and the second area of ​​interest interface is used to display the area that needs to be photographed, which is the control area of ​​the above-mentioned shooting area that needs to be diagnosed.

[0020] Furthermore, the diagnosis interface may further include a scan guide interface for displaying the unit scan data assurance status of the probe.

[0021] In addition, the above-mentioned central control device can output a diagnostic interface, and the above-mentioned diagnostic interface outputs a chromophore image for displaying the distribution status of the above-mentioned chromophore. The above-mentioned diagnostic interface can display side by side the chromophore image of the diagnostic area generated based on the data collected using the above-mentioned first region of interest interface and the chromophore image of the control area generated based on the data collected using the above-mentioned second region of interest interface.

[0022] Furthermore, the diagnosis interface may display the chromophore image of the diagnosis region and the chromophore image of the control region side by side according to the type of the chromophore.

[0023] Furthermore, a breast cancer diagnosis method according to another embodiment of the present invention utilizes a breast cancer diagnosis system based on near-infrared measurement technology. The breast cancer diagnosis method includes the following steps: receiving optical data of reflected light from a target detected by a probe, calculating the chromophore concentration of the target for each chromophore based on the optical data; generating a chromophore image representing the distribution of the calculated chromophore concentration values; and outputting the generated chromophore image via a display. In the step of calculating the chromophore concentration, the chromophore concentration of the target is calculated by inputting the measured values ​​of each wavelength of the reflected light detected by the probe into a learning model. The learning model performs machine learning based on training data in which the measured values ​​of each wavelength of light are matched to the concentrations of multiple chromophore substances.

[0024] Specific matters of other embodiments for solving the technical problems are included in the description and drawings.

[0025] Effects of the Invention

[0026] According to the above technical solution of the present invention, in the breast cancer diagnosis system of the present invention, since the probe has a wireless structure and is configured with multiple channel signal processing units to collect measurement data of a large area of ​​the chest at one time, it has the effect of conveniently photographing the chest.

[0027] Furthermore, since a diagnosis interface for accurately photographing the chest using a probe is output to the display under the control of the central control device, the chest can be accurately photographed.

[0028] Furthermore, since the chromophore image of the diagnosis area and the chromophore image of the control area are simultaneously output to the display under the control of the central control device, breast cancer can be easily identified by comparing them simultaneously.

[0029] Furthermore, since a diagnostic interface is output to the display according to the type of each chromophore under the control of the central control device, the diagnostic interface outputs the chromophore image of the diagnostic area and the chromophore image of the control area. Therefore, the chromophore image of the diagnostic area and the chromophore image of the control area can be compared according to the type of each chromophore, thereby having the effect of accurately diagnosing breast cancer. BRIEF DESCRIPTION OF THE DRAWINGS

[0030] Figure 1 FIG. 1 is a block diagram illustrating a breast cancer diagnosis system according to an embodiment of the present invention.

[0031] Figure 2 To show Figure 1 Figure 1 is an example of a probe.

[0032] Figure 3 To show Figure 2 Diagram of a probe in contact with a target to collect optical data.

[0033] Figure 4 To show Figure 1 FIG. 1 is another example of a probe.

[0034] Figure 5 The figure shows the first decoder and the second decoder of the first control unit that transmit and receive data with the driver chip of the channel signal processing unit.

[0035] Figure 6 To show Figure 1 Block diagram of the data processing unit of the central control device.

[0036] Figure 7 To show that Figure 1 A block diagram of an interface output to a display unit of a display under the control of a second control unit of a central control device.

[0037] Figure 8 To show Figure 7 Block diagram of the diagnosis interface.

[0038] Figure 9 To show the output to the display unit of the display Figure 8 An example of the diagnosis interface of .

[0039] Figure 10 To show that Figure 8 The scan guide interface shows a graph of the optical data collected by the signal processing unit for each channel.

[0040] Figure 11 To show that Figure 8 The Scan Guide screen displays a diagram of the probe's movement guide for collecting optical data.

[0041] Figure 12 To show that Figure 7 Figure 1. Output of chromophore image in the diagnostic interface of .

[0042] Figure 13 To show that Figure 7 In the diagnosis interface, a chromophore image of the diagnosis area and a chromophore image of the control area are output according to the type of chromophore.

[0043] Figure 14 This is a diagram showing another embodiment of outputting a diagnosis interface to the display unit of a display. DETAILED DESCRIPTION

[0044] Below, embodiments of the present invention will be described in detail with reference to the accompanying drawings so that those skilled in the art can easily implement the present invention. However, the present invention is not limited to the embodiments described herein and can be implemented in a variety of different forms. Furthermore, to clearly illustrate the present invention, portions not relevant to the description are omitted from the accompanying drawings. Similar portions are designated by similar reference numerals throughout the specification.

[0045] Throughout the specification of the present invention, when it is mentioned that a certain part is “connected” to another part, it includes not only the case of “direct connection” but also the case of “electrical connection” with other devices in between.

[0046] Throughout the specification of the present invention, when it is mentioned that a certain component is located “on” another component, it includes not only a case where the certain component is in contact with the other component, but also a case where other components exist between the two components.

[0047] Throughout this specification of the present invention, when it is mentioned that a part "includes" a certain structural element, unless otherwise explicitly stated, it means that other structural elements may also be included, rather than excluding other structural elements. Degree-related terms such as "approximately" and "actually" used throughout the specification of the present invention are used to mean equal to or approximately the numerical value when the inherent manufacturing and material tolerances are given in the mentioned meaning, and are used to prevent unscrupulous infringers from making improper use of the disclosure content that mentions accurate or absolute numerical values ​​for ease of understanding. The degree-related terms "~ step" or "step of ~" used throughout this specification do not have the meaning of "step for ~".

[0048] Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings and the following description. However, the present invention is not limited to the embodiments described herein and may also be embodied in other forms. Throughout the specification, the same reference numerals represent the same structural elements.

[0049] The structure of the breast cancer diagnosis system according to the embodiment of the present invention will be described below.

[0050] Figure 1 FIG. 1 is a block diagram illustrating a breast cancer diagnosis system according to an embodiment of the present invention.

[0051] Reference Figure 1 To illustrate, the breast cancer diagnostic system 1 of the present invention may include: a probe 1000 for collecting optical data based on the various chromophore substances in breast tissue; a display 2000 for outputting an interface and images; and a central control device 3000 for controlling the operation of the probe 1000 and the output of the display 2000 and processing the data.

[0052] Figure 2 To show Figure 1 Figure 1 is an example of a probe.

[0053] First, refer to Figure 1 and Figure 2 The structure of the probe 1000 will be described.

[0054] The probe 1000 may include a channel signal processing unit 1100 , a notification unit 1300 , a first communication unit 1500 , a first control unit 1600 , and a body.

[0055] N channel signal processing units 1100 can be arranged in the probe 1000 (N is a natural number greater than 1), and can include: a light irradiation module 1120, which irradiates incident light to the chest; a light collection module 1160, which collects measurement values ​​(hereinafter referred to as light data) of information such as the wavelength of light reflected from the incident light irradiated to the chest (hereinafter referred to as reflected light); and a driving chip.

[0056] The light irradiation module 1120 may include light output devices such as a laser diode (LD), a light emitting diode (LED), and a vertical cavity surface emitting laser (VCSEL), which can output incident light with wavelengths of different lengths in the near infrared ray region.

[0057] For example, light irradiation module 1120 may be configured to output incident light divided into eight types according to wavelength length. In this case, if one light output device constituting light irradiation module 1120 is capable of outputting light having eight types of wavelengths, light irradiation module 1120 may be composed of one light output device. Alternatively, if one light output device constituting light irradiation module 1120 is capable of outputting light having four types of wavelengths, light irradiation module 1120 may be composed of two light output devices each outputting light having a different wavelength.

[0058] On the other hand, the number of types of incident light of each wavelength output from the light irradiation module 1120 can be determined based on the number of chromophore types present in the breast. Since chromophores effectively absorb light of a specific wavelength depending on their type, the concentration of each chromophore type present in the breast can be measured by irradiating the breast with incident light of a wavelength that effectively absorbs each chromophore and collecting and analyzing the reflected light.

[0059] The light collection module 1160 may include light collection devices such as a photodiode, a phototransistor, a photomultiplier tube (PMT), and a photo cell that can collect light data by receiving light.

[0060] The light data of the reflected light collected by the light collection module 1160 may be transmitted to the central control device 3000 to calculate the concentration of the chromophore.

[0061] Figure 3 To show Figure 2 Diagram of a probe in contact with a target to collect optical data.

[0062] Specifically, refer to Figure 3 To illustrate, the light irradiation module 1120 and the light collection module 1160 can be set on the probe 1000 in a manner of being exposed on a specified surface of the probe 1000, so that when the specified surface of the probe 1000 contacts the optical data collection target 10 (hereinafter referred to as the target body) such as the chest, the light irradiation module 1120 and the light collection module 1160 can contact the target body 10.

[0063] Furthermore, when the incident light irradiated from the light irradiation module 1120 is reflected inside the object 10, the light collection module 1160 may collect light data of the reflected light. The light data may include information related to the wavelength, intensity, etc. of the reflected light.

[0064] Figure 4 To show Figure 1 FIG. 1 is another example of a probe.

[0065] Reference Figure 4 , the probe 1000 may include at least one channel signal processing unit 1100 .

[0066] For example, Figure 4 As shown, the probe 1000 may include a plurality of channel signal processing units 1100 , so that a plurality of light irradiation modules 1120 and a plurality of light collection modules 1160 are exposed to a prescribed surface of the probe 1000 .

[0067] For example, N channel signal processing units 1100 can be arranged horizontally along an axis of the probe 1000. Multiple light irradiation modules 1120 and multiple light collection modules 1160 of adjacent channel signal processing units 1100 can be arranged adjacent to each other, such that the multiple light irradiation modules 1120 are arranged in a row parallel to the axis, and the multiple light collection modules 1160 and the multiple light irradiation modules 1120 can be arranged in a row parallel to the axis, separated by a predetermined distance. In this case, the penetration depth of near-infrared light can be adjusted based on the separation distance between the light collection modules 1160 and the light irradiation modules 1120, thereby adjusting the measurement depth within the measurement object. For example, the penetration depth of near-infrared light is approximately half the separation distance. Therefore, the optimal measurement depth can be set by setting an appropriate separation distance between the light collection modules 1160 and the light irradiation modules 1120.

[0068] In other words, the distances between the light irradiation modules 1120 and the light collection modules 1160 included in each channel signal processing unit 1100 can be the same, so that multiple light irradiation modules 1120 are arranged in a row along a first direction on the specified surface of the probe 1000, and multiple light collection modules 1160 are arranged in a row along a second direction parallel to the first direction on the specified surface of the probe 1000.

[0069] As described above, the probe 1000 includes at least one channel signal processing unit 1100 , so that when the probe 1000 can contact the target 10 and collect optical data, optical data of a large area of ​​the target 10 can be collected through one contact.

[0070] On the other hand, the arrangement of the plurality of light irradiation modules 1120 and the light collection modules 1160 included in the multi-channel signal processing unit 1100 provided in the probe 1000 is not limited to the above-described arrangement of the light irradiation modules 1120 and the light collection modules 1160 .

[0071] The driving chip 1180 may sequentially output driving signals for driving the light irradiation module 1120 according to control signals of the first control unit 1600 described later, and transmit light data of the reflected light detected by the light collection module 1160 to the first control unit 1600 .

[0072] Furthermore, the driving chip 1180 of each channel signal processing unit 1100 may sequentially output 4 to 12 driving signals, so that the light irradiation module 1120 sequentially outputs 4 to 12 beams of light with different wavelengths.

[0073] The notification unit 1300 may include a flashing light emitting diode, a liquid crystal display, etc., and may be provided on the outer shell of the probe 1000 body. It may function to notify the user of the working status of the probe 1000, etc.

[0074] For example, when the channel signal processing unit 1100 of the probe 1000 contacts the chest and completes collecting light data, the notification unit 1300 can notify the user that the probe 1000 has completed collecting light data by flashing a flashing light emitting diode or displaying information related to the completion of collecting light data on a liquid crystal display.

[0075] The first communication unit 1500 may be composed of an existing communication module capable of transmitting and receiving data with a device outside the probe 1000 , and may include a wireless communication module such as WiFi or Bluetooth.

[0076] For example, when the probe 1000 is configured to be wirelessly connected to the central control device 3000, control data related to the operation of the probe 1000, etc., transmitted from the central control device 3000, can be received via the first communication unit 1500. Furthermore, optical data of the chest collected by the probe 1000 can be transmitted to the central control device 3000 via the first communication unit 1500.

[0077] The first control unit 1600 can control the actions of the channel signal processing unit 1100, the notification unit 1300, and the first communication device 1500, and can be implemented by a device capable of processing data, such as a processor. For example, a processor can refer to a data processing device embedded in hardware, which has a physical structured circuit to execute the function expressed by the code or instruction included in the program. As an example of such a data processing device embedded in hardware, a microprocessor, a central processing unit (CPU), a processor core, a multiprocessor, an application-specific integrated circuit (ASIC), a field programmable gate array (FPGA), and other processing devices can be included, but the scope of the present invention is not limited thereto.

[0078] In addition, the first control unit 1600 may further include a first decoder 1620 and a second decoder 1660 for transmitting and receiving data with the driving chip 1180 of the channel signal processing unit 1100 .

[0079] Figure 5 11 is a diagram showing a first decoder and a second decoder of a first control unit that transmits and receives data with a driver chip 1180 of a channel signal processing unit.

[0080] On the other hand, refer to Figure 5To illustrate, the first control unit 1600 may include: a first decoder 1620, which sequentially transmits control signals that cause the driver chips 1180 of each channel signal processing unit 1100 to operate; and a second decoder 1620, which sequentially receives and outputs light data of the reflected light output by each driver chip 1180.

[0081] Furthermore, as the first control unit 1600 receives all light data corresponding to the reflected light of the unit scan described later through each channel signal processing unit 1100, a control signal can be transmitted to the notification unit 1300 such as a flashing light emitting diode and a liquid crystal display to indicate that the unit scan has been completed.

[0082] The main body may be composed of a housing capable of accommodating the channel signal processing unit 1100, the notification unit 1300, the first communication unit 1500, and the first control unit 1600. A contact surface may be provided on the lower surface. The light irradiation module 1120 and the light collection module 1160 may be configured to be exposed to the outside through an opening formed in the contact surface.

[0083] Next, the structure of the display 2000 will be described.

[0084] Reference Figure 1 For illustration, the display 2000 may include a display portion 2100 and a second communication portion 2300 .

[0085] The display unit 2100 may be composed of a conventional monitor, liquid crystal display, or the like that can output various image data in the form of images or an output interface.

[0086] The second communication unit 2300 may be composed of a general communication module capable of transmitting and receiving data with a device outside the display 2000 .

[0087] For example, when the display 2000 is configured to be wirelessly connected to the central control device 3000 , image data and the like transmitted from the central control device 3000 may be received through the second communication unit 2300 .

[0088] Furthermore, the display 2000 may further include a touch input module, thereby controlling the actions of various interfaces displayed on the display 2000 and the actions of the central control device 3000 .

[0089] Next, the structure of the central control device 3000 will be described.

[0090] Reference Figure 1 For illustration, the central control device 3000 may include: a data processing unit 3100 for calculating and processing data; a second control unit 3300 for controlling the operation of the probe 1000 and the display 2000; and a third communication unit 3500.

[0091] The central control device 3000 can perform the following tasks, namely, controlling the movement of the probe, receiving light data of the reflected light detected by the probe, calculating the chromophore concentration of the target body for each chromophore based on the light data, and generating a chromophore image for representing the concentration value distribution of each chromophore. The above-mentioned central control device 3000 may include: a memory with a built-in program for performing the above-mentioned tasks; and various processors for running the program.

[0092] The memory may temporarily or permanently store data processed by the processor, and may include volatile storage media or non-volatile storage media, but the scope of the present invention is not limited thereto.

[0093] A processor is used to run a program, and for example, may refer to a data processing device embedded in hardware, which has physically structured circuitry to execute the functions expressed by the code or instructions included in the program. Examples of such a data processing device embedded in hardware include a microprocessor, a central processing unit (CPU), a processor core, a multiprocessor, an application-specific integrated circuit (ASIC), a field programmable gate array (FPGA), and other processing devices, but the scope of the present invention is not limited thereto.

[0094] Figure 6 To show Figure 1 Block diagram of the data processing unit of the central control device.

[0095] Reference Figure 6 For illustration, the data processing unit 3100 may include: a calculation module 3120 for calculating chromophore concentration-related data based on the light data transmitted by the probe 1000; and a generation module 3160 for generating a chromophore image for representing the concentration value distribution of the chromophore based on the calculated chromophore concentration.

[0096] The calculation module 3120 can receive light data (hereinafter referred to as unit scan data) collected by each channel signal processing unit 1100 and calculate the chromophore concentration based on each unit scan data. The unit scan data may include measurement values ​​of reflected light reflected from light of multiple different wavelengths output by the light irradiation module 1120 of each channel signal processing unit 1100.

[0097] For example, the calculation module 3120 may calculate the chromophore concentration using a learning model that has been trained through machine learning (hereinafter referred to as a learning model).

[0098] The learning model can be learned based on training data, and the above training data may include incident light information with a wavelength of a specific length, light data information of reflected light collected when the chest is irradiated with a wavelength of the specific length, and information related to the chromophore concentration corresponding to the collected light data information.

[0099] Specifically, the training data consists of a one-to-one match between the measured wavelengths of reflected light and the concentrations of multiple chromophore substances. For example, when incident light of wavelengths 1 through 8 is sequentially incident, the measured values ​​of the reflected light (e.g., light intensity) are a1 through a8. Based on these measured values, the concentrations of individual chromophore substances (b1 through bn) are calculated using known chromophore calculation methods. In this case, the method of calculating the chromophore concentration in a turbid medium by measuring its absorption coefficient and scattering coefficient in the near-infrared region is prior art, and therefore a detailed description thereof is omitted.

[0100] For example, in the present invention, when the concentrations of four chromophore substances, namely water (H2O), lipids, oxyhemoglobin (O2Hb), and deoxyhemoglobin (HHb), need to be calculated based on the measured values ​​of eight types of reflected light, the measured values ​​(a1 to a8) of the light data for each type of reflected light can be labeled with the calculated concentrations of each chromophore (b1, b2, b3, and b4) and used as learning data. A learning model can be constructed by collecting multiple such learning data and applying them to a machine learning algorithm.

[0101] In a learning model that performs machine learning based on this training data, specific light data collected by irradiating incident light with a specific wavelength is input, and the specific chromophore concentration in the chest can be calculated by comparing the input incident light and light data information with the corresponding training data.

[0102] On the other hand, the collected light data may be input to the learning model after being calibrated using calibration values.

[0103] For example, the calibration value can be a value obtained by dividing the theoretical measurement value of light data of reflected light collected by irradiating incident light to an object (hereinafter referred to as the reference object) serving as a reference for measuring the calibration value by the light irradiation module 1120 by the actual measurement value of light data of reflected light collected by irradiating incident light to the reference object.

[0104] Also, the collected light data may be calibrated by irradiating incident light to the chest using the light irradiation module 1120 and multiplying a measurement value of light data of reflected light collected by the light collection module 1160 by a calibration value.

[0105] If the light data calibrated as above is input into the learning model, the chromophore concentration can be calculated.

[0106] The generating module 3160 may generate a chromophore image according to the chromophore concentration, the chromophore image including at least one different image-related information of color, brightness, and saturation.

[0107] For example, the generating module 3160 may generate a chromophore image, in which the concentrations of each chromophore calculated based on each unit scan data may be displayed as a separate image on a two-dimensional coordinate system (hereinafter referred to as a unit frame image).

[0108] Furthermore, the generation module 3160 may also utilize a conventional interpolation algorithm to generate image-related data (hereinafter referred to as image data). Examples of interpolation algorithms include linear interpolation, bilinear interpolation, cubic interpolation, and bicubic interpolation.

[0109] For example, when generating a chromophore image with a first saturation at a first position on the chest and a chromophore image with a second saturation at a second position on the chest, image data estimated using a difference algorithm (hereinafter referred to as estimated image data) can be generated so that the middle position between the first position and the second position corresponds to image data with an average saturation of the first saturation and the second saturation.

[0110] The second control unit 3300 may control the operation of the probe 1000 by transmitting control data for controlling the operation of the probe 1000 to the probe 1000 .

[0111] Specifically, the second control unit 3300 can control the operation of the light irradiation module 1120 and the notification unit 1300 of the channel signal processing unit 1100 of the probe 1000 , and can control the probe 1000 to transmit optical data to the central control device 3000 .

[0112] For example, the second control unit 3300 can control the flashing of the incident light output by the light irradiation module 1120 so that the probe 1000 can irradiate the incident light onto the chest or stop irradiating the incident light, and can control the intensity and wavelength of the incident light output by the light irradiation module 1120.

[0113] Furthermore, when the probe 1000 includes a plurality of channel signal processing units 1100 , the second control unit 3300 may control the irradiation order of the incident light so that the plurality of light irradiation modules 1120 irradiate the incident light in a free order or sequentially.

[0114] As another example, when the probe 1000 is in contact with the chest, the multiple channel signal processing units 1100 have completed collecting light data, and the second control unit 3300 can control the operation of the notification unit 1300 to enable the notification unit 1300 to notify the completion of light data collection.

[0115] As another example, the second control unit 3300 can control the probe 1000 so that the probe 1000 transmits the collected optical data to the central control device 1500 through the first communication unit 1500 .

[0116] The second control unit 3300 may control the output of the display unit 2100 by transmitting control data for controlling the operation of the display 2000 to the display 2000 .

[0117] Figure 7 To show that Figure 1 A block diagram of an interface output to a display unit of a display under the control of a second control unit of a central control device.

[0118] Reference Figure 7 For illustration, the second control unit 3300 may control the display unit 2100 to output an interface to the display unit 2100 , which includes a diagnosis interface 3320 for guiding breast cancer diagnosis and a diagnosis interface 3360 for diagnosing breast cancer.

[0119] Figure 8 To show Figure 7 Block diagram of the diagnosis interface.

[0120] Reference Figure 8 For illustration, the diagnosis interface 3320 may include a photographing guide interface 3322 and a scanning guide interface 3326 .

[0121] Figure 9 To show the output to the display unit of the display Figure 8 An example of the diagnosis interface.

[0122] Reference Figure 9 For illustration, the shooting guide interface 3322 may display the left chest area and the right chest area respectively.

[0123] Specifically, the shooting guide interface 3322 may include: a first region of interest (ROI) interface 3322-1, which displays a first part to be diagnosed for breast cancer in a first coordinate system; a first chest image 3322-2 containing the first part; a second region of interest (ROI) interface 3322-3, which displays a second part for comparison with the first part in a second coordinate system; and a second chest image 3322-4 including the second part.

[0124] The second chest image 3322-4 is an image of the other chest of the examinee's two chests, excluding the first chest image 3322-2. The second region of interest (ROI) interface 3322-3 can be a portion of the second chest that is symmetrical to the first region of interest (ROI) interface 3322-1, with the center of the user's two chests as a reference. In this case, the first region of interest interface represents the area to be scanned and can be directly set by the user of the apparatus of the present invention. On the other hand, the second region of interest interface is provided for scanning a control area as a comparison object and can be directly set by the user, or it can be automatically set to an area that is a mirror reflection of the first region of interest interface after the first region of interest interface is set.

[0125] The scan guide interface 3326 may be configured to guide the operation of the probe 1000 so that the user can use the probe 1000 to collect optical data inside the chest, and may be composed of a third coordinate system that magnifies and displays the first portion 3322 - 1 or the second portion 3322 - 3 .

[0126] Specifically, when the user uses the probe 1000 to collect optical data of the first chest 3322-2, the scanning guide interface 3326 may include coordinates related to multiple positions where the multiple channel signal processing units 1100 contact the first part 3322-1 (hereinafter referred to as contact positions) and coordinates related to positions where the multiple channel signal processing units 1100 are expected to contact the first part 3322-1 (hereinafter referred to as expected contact positions).

[0127] Furthermore, when the user uses the probe 1000 to collect optical data of the second chest 3322-4, the scan guide interface 3326 may also include coordinates related to the contact position of the multiple-channel signal processing unit 1100 and the second part 3322-3 and coordinates related to the expected contact position of the multiple-channel signal processing unit 1100 and the second part 3322-3.

[0128] Figure 10 To show that Figure 8 The scan guide interface shows a graph of the optical data collected by the signal processing unit for each channel.

[0129] For example, refer to Figure 10For illustration, when the probe 1000 includes five channel signal processing units 1100 , the five circular coordinates in the first row may be coordinates related to contact positions between each channel signal processing unit 1100 of the probe 1000 and the first portion 3322 - 1 or the second portion 3322 - 3 .

[0130] Also, the circular coordinates from the second row to the fifth row may be coordinates related to expected contact positions between each channel signal processing unit 1100 of the probe 1000 and the first portion 3322 - 1 or the second portion 3322 - 3 .

[0131] On the other hand, when the single-channel signal processing unit 1100 completes collecting optical data, the scan guide interface 3326 can be controlled by the second control unit 3300 to display the completion of optical data collection at a position on the third coordinate system corresponding to the contact position where optical data collection is completed. In other words, the acquisition status of the unit scan data of the probe 1000 can be displayed.

[0132] For example, refer to Figure 10 In part (a), when the signal processing units 1100 of each channel of the probe 1000 that contacts the first part 3322-1 or the second part 3322-3 at the position corresponding to the five circular coordinates of the first row complete the detection of the light data of the position of the first part 3322-1 or the second part 3322-3 corresponding to the circular coordinates of the first row, the second control unit 3300 can control the display unit 2100 to light up the circular coordinates of the first row, the first column, the third column.

[0133] As another example, refer to Figure 10 Part (b) of Figure 10 Similarly to part (a), when the channel signal processing unit 1100 that completes the detection of the light data completes the detection of the light data of the position of the first part 3322-1 or the second part 3322-3 corresponding to the circular coordinates of the first row, fourth column to fifth column, the second control unit 3300 can control the display unit 2100 to light up the circular coordinates of the first row, fourth column to fifth column.

[0134] Furthermore, when the probe 1000 contacts the first part 3322-1 or the second part 3322-3, so that the multiple channel signal processing units 1100 constituting the probe 1000 have completed collecting optical data, the scanning guide interface 3326 can be controlled by the second control unit 3300 to guide the movement of the probe 1000, so that the probe 1000 moves on the first part 3322-1 or the second part 3322-3 and collects optical data.

[0135] Figure 11 To show that Figure 8 The Scan Guide screen displays a diagram of the probe's movement guide for collecting optical data.

[0136] For example, refer to Figure 11 In part (a), the probe 1000 can be positioned so that the five-channel signal processing units are located at the first portion 3322-1 or the second portion 3322-3 corresponding to the five circular coordinates in the third row. Alternatively, the position of the probe 1000 can be controlled by the second control unit 3300 to be displayed as a solid line on the third coordinate system.

[0137] Furthermore, when the multi-channel signal processing unit 1100 of the probe 1000 that contacts the chest with the position of the first part 3322-1 or the second part 3322-3 corresponding to the five circular coordinates of the third row completes the detection of the light data of the position of the first part 3322-1 or the second part 3322-3 corresponding to the circular coordinates of the first to fifth columns of the third row, the second control unit 3300 can control the display unit 2100 to display a dotted line of the moving position of the probe 1000 around the fourth column.

[0138] Reference Figure 11 In part (b), as the probe 1000 moves to the position guided by the dotted line, the solid line indicating the position of the probe 1000 may also move accordingly.

[0139] Next, refer to Figure 11 In part (c), when the probe 1000 moves to the point where the solid line representing the position of the probe 1000 coincides with the dotted line around the fourth column, the channel signal processing unit 1100 of the moved probe 1000 collects optical data at the position of the first portion 3322-1 or the second portion 3322-3 corresponding to the circular coordinates in the fourth column.

[0140] On the other hand, the method of indicating the position of the probe 1000 and the method of guiding the movement position of the probe 1000 under the control of the second control unit 3300 are not limited to the above-mentioned methods.

[0141] The diagnosis interface 3360 may include a chromophore image for displaying the distribution state of the chromophore. That is, the diagnosis interface 3360 may be controlled by the second control unit 3300 to output the chromophore image to the display unit 2100 in the form of an image.

[0142] Figure 12 To show that Figure 7 Figure 1. Output of chromophore image in the diagnostic interface of .

[0143] Reference Figure 12For explanation, the diagnostic interface 3360 can be controlled by the second control unit 3300 to simultaneously output the chromophore image 3362 of the diagnostic area and the chromophore image 3366 of the control area, wherein the chromophore image 3362 of the diagnostic area is a first portion 3322-1 generated based on data collected using the first region of interest (ROI) interface, and the chromophore image 3366 of the control area is a second portion 3322-3 generated based on data collected using the second region of interest (ROI) interface.

[0144] As described above, the chromophore image 3362 of the diagnosis area and the chromophore image 3366 of the control area are simultaneously output on the diagnosis interface 3360, allowing the user to easily compare the two images, thereby quickly and accurately diagnosing breast cancer in the first site 3322-1. For ease of description, the same image is output in the figures. However, if cancer is present, the chromophore image 3362 of the diagnosis area and the chromophore image 3366 of the control area will be output differently.

[0145] The chromophore image 3362 of the diagnosis region and the chromophore image 3366 of the control region may include an estimated image. The estimated image may be the estimated image data generated by the generation module 3160 of the second control unit 3300 and outputted on the display unit 2100 in the form of an image.

[0146] For example, when the generation module 3160 uses the above-mentioned difference algorithm to generate inferred image data as image data corresponding to the partial positions of the first part 3322-1 and the second part 3322-3 where no light data is collected, the second control unit 3300 can control the display unit 2100 to output the inferred image as an image corresponding to the partial positions of the first part 3322-1 and the second part 3322-3 where no light data is collected.

[0147] That is, an estimated image generated based on estimated image data estimated by a difference algorithm can be displayed in the blank space between the coordinates.

[0148] As such, since the chromophore image 3362 of the diagnosis area and the chromophore image 3366 of the control area output in the diagnosis interface 3360 can output reasonably estimated images as images related to the position where no light data is collected, the user can continuously obtain continuous images related to the chromophore concentration to easily diagnose breast cancer.

[0149] On the other hand, the diagnosis interface 3360 may be controlled by the second control unit 3300 to output chromophore images according to the types of chromophores.

[0150] Figure 13 To show that Figure 7In the diagnosis interface, a chromophore image of the diagnosis area and a chromophore image of the control area are output according to the type of chromophore.

[0151] For example, refer to Figure 13 To explain, the diagnosis interface 3360 may be controlled by the second control unit 3300 to output a chromophore image of the diagnosis region and a chromophore image of the control region according to the type of chromophore.

[0152] In this way, by simultaneously outputting the chromophore image of the diagnosis area and the chromophore image of the control area according to the type of each chromophore in the diagnosis interface 3360, the user can accurately compare the chromophore image of the diagnosis area and the chromophore image of the control area according to the type of each chromophore, thereby diagnosing breast cancer more accurately.

[0153] Figure 14 This is a diagram showing another embodiment of outputting a diagnosis interface to the display unit of a display.

[0154] The overall interface structure of the diagnosis interface 3320 of another embodiment of the present invention is similar to Figure 9 The embodiments shown are almost identical. Figure 14 As shown, in the present invention, multiple region of interest interfaces 3322-1 and 3322-3 can be displayed on the chest image, and thus light data can be collected for each region of interest interface 3322-1 and 3322-3.

[0155] For example, the user may set four region of interest interfaces 3322-1 for the first side of the chest 3322-2 and thereby set four region of interest interfaces 3322-3 for the second side of the chest 3322-4 in order to collect light data of a control area.

[0156] The following describes the function and effect of the breast cancer diagnosis system of the present invention.

[0157] Following the guidance of the diagnosis interface 3320 outputted by the display unit 2100 of the display 2000, the user uses the probe 1000 to collect optical data of a first portion 3322-1 of a first breast 3322-2 to be diagnosed for breast cancer and a second portion 3322-3 of a second breast 3322-4 for comparison.

[0158] In this case, the probe 1000 can be moved according to the guidance of the shooting guide interface 3322 and the scanning guide interface 3326 of the diagnosis interface 3320 to conveniently and effectively collect optical data of the first part 3322-1 and the second part 3322-3.

[0159] The collected light data of the first portion 3322 - 1 and the second portion 3322 - 3 are transmitted to the central control device 3000 . The central control device 3000 calculates the chromophore concentration based on the received light data and generates a chromophore image based on the calculated chromophore concentration.

[0160] After generating the chromophore image, the central control device 3000 controls the display 2000 to output a diagnosis interface 3360 through the display portion 2100 of the display 2000 , which includes the chromophore image of the diagnosis area and the chromophore image of the control area.

[0161] The chromophore image of the diagnosis area and the chromophore image of the control area can be output simultaneously in the diagnosis interface 3360. The user can compare the chromophore image of the diagnosis area and the chromophore image of the control area output in the diagnosis interface 3360 at the same time, so as to easily and quickly diagnose breast cancer in the first site 3322-1.

[0162] Furthermore, since the diagnostic interface 3360 can simultaneously output the chromophore image of the diagnostic area and the chromophore image of the control area according to the type of each chromophore, the user can compare and analyze the chromophore image of the diagnostic area and the chromophore image of the control area according to the type of each chromophore, thereby accurately diagnosing breast cancer.

[0163] As described above, in the breast cancer diagnosis system of the present invention, since the probe has a wireless structure and is equipped with multiple channel signal processing units to collect measurement data of a large area of ​​the breast at one time, it has the effect of conveniently photographing the breast.

[0164] Furthermore, since a diagnosis interface for accurately photographing the chest using a probe is output to the display under the control of the central control device, the chest can be accurately photographed.

[0165] Furthermore, since the chromophore image of the diagnosis area and the chromophore image of the control area are simultaneously output to the display under the control of the central control device, the chromophore image of the diagnosis area and the chromophore image of the control area can be compared at the same time to easily identify breast cancer.

[0166] Furthermore, since a diagnostic interface is output to the display according to each chromophore type under the control of the central control device, the diagnostic interface outputs a chromophore image of the diagnostic area and a chromophore image of the control area. Therefore, the chromophore image of the diagnostic area and the chromophore image of the control area can be compared according to each chromophore type, thereby achieving the effect of accurately diagnosing breast cancer.

[0167] The breast cancer diagnosis method of one embodiment of the present invention can be implemented in the form of a recording medium including computer-executable instructions such as computer-executable program modules. Computer-readable media can be any available media that can be accessed by a computer, including volatile and non-volatile media, removable and non-removable media. Furthermore, computer-readable media can include computer storage media. Computer storage media includes all volatile and non-volatile, removable and non-removable media implemented in any method or technology for storing information such as computer-readable instructions, data structures, program modules, or other data. The above description of the method and system of the present invention is based on specific embodiments, but some or all of their structural elements or actions can be implemented by a computer system with a general hardware architecture.

[0168] The above description of the present invention is for illustrative purposes only. A person skilled in the art will appreciate that the present invention can be readily adapted to other specific forms without altering the technical concept or essential features of the present invention. Therefore, the embodiments described above should be understood in all respects to be illustrative and not restrictive. For example, various structural elements described as being singular may be implemented in a dispersed manner, and similarly, structural elements described as dispersed may also be implemented in a combined manner.

[0169] The scope of the present invention is determined by the scope of the appended claims rather than the detailed description above, and all changes or modifications derived from the meaning, scope and equivalent concepts of the claims should be interpreted as being included within the scope of the present invention.

Claims

1. A breast cancer diagnosis system using near-infrared measurement technology, characterized in that: include: The probe sequentially outputs light of multiple wavelengths in the near-infrared region toward a target object, receives reflected light from the target object, and sequentially processes the reflected light; a central control device that controls the operation of the probe, receives optical data of the reflected light detected by the probe, calculates the chromophore concentration of the target object for each chromophore based on the optical data, and generates a chromophore image representing the concentration distribution of each chromophore; and The display outputs the image generated by the above-mentioned central control device, in N channel signal processing units are arranged in the probe, including at least one light irradiation module and at least one light collection module, wherein N is a natural number greater than 1. Each of the channel signal processing units operates in sequence to generate the light data of the reflected light, thereby generating unit scanning data containing a total of N optical data. The N channel signal processing units are arranged in a horizontal direction along one axis of the probe, and The plurality of light irradiation modules and the plurality of light collection modules of the adjacent channel signal processing units are arranged adjacent to each other so that the plurality of light irradiation modules are arranged in a row parallel to the one axis, and the plurality of light collection modules are spaced a predetermined distance from the plurality of light irradiation modules and arranged in a row parallel to the one axis. The central control device sequentially receives the unit scan data transmitted from the probe, calculates the chromophore concentration of each unit scan data using a learning model, and displays the concentration of each chromophore on a two-dimensional coordinate to generate a unit frame image, and wherein the learning model performs machine learning based on training data, wherein the measured value of each wavelength of light is matched to the concentration of each of a plurality of chromophore materials, The central control device outputs a diagnosis interface for guiding the scanning steps of the probe. The above-mentioned diagnosis interface includes a shooting guide interface showing the left chest area and the right chest area respectively, and The first ROI interface and the second ROI interface are displayed in the above-mentioned shooting guide interface. The first ROI interface is used to display the shooting area that needs to be diagnosed, and the second ROI interface is used to display the area that needs to be photographed, which is a control area for the above-mentioned shooting area that needs to be diagnosed.

2. The breast cancer diagnosis system according to claim 1, wherein: The above probes include: a main body comprising the plurality of channel signal processing units, a first control unit, and a first communication unit, wherein the first control unit controls the operation of the channel signal processing units, and the first communication unit transmits output data of the first control unit to the outside; and The contact surface is arranged on the lower surface of the above-mentioned body, The light irradiation module and the light collection module of the channel signal processing unit are arranged in a state of being exposed to the outside through an opening formed in the contact surface.

3. The breast cancer diagnosis system according to claim 2, characterized in that: Each of the above channel signal processing sections includes: At least one of the light irradiation modules is arranged adjacent to each other; The light collecting module is arranged at a predetermined distance from the light irradiating module; and The driving chip sequentially outputs driving signals for driving the light irradiation module according to the control signal of the first control unit, and transmits the light data of the reflected light detected by the light collection module to the first control unit. The driving chip of each of the channel signal processing units sequentially outputs 4 to 12 driving signals, so that the light irradiation module sequentially outputs 4 to 12 beams of light with different wavelengths.

4. The breast cancer diagnosis system according to claim 2, wherein: The first control unit includes: A first decoder sequentially transmits control signals for operating the driver chips of the channel signal processing units; and The second decoder sequentially receives and outputs the light data of the reflected light output by each of the driving chips.

5. The breast cancer diagnosis system according to claim 2, wherein: The probe further includes a flashing light emitting diode or a liquid crystal display on the housing of the body. As the first control unit receives all the light data of the reflected light corresponding to the unit scan through each of the channel signal processing units, the flashing light emitting diode or the liquid crystal display indicates that the unit scan has been completed.

6. The breast cancer diagnosis system according to claim 1, wherein: The unit scan data includes the light data of the reflected light based on the light of 4 or more and 12 or less different wavelengths outputted by the light irradiation module of each of the channel signal processing units. The data in the blank spaces between each coordinate represents the value calculated by the interpolation algorithm.

7. The breast cancer diagnosis system according to claim 1, wherein: The diagnosis interface further includes a scan guide interface for displaying the unit scan data assurance status of the probe.

8. The breast cancer diagnosis system according to claim 1, wherein: The above-mentioned diagnosis interface displays N ROI interfaces for displaying the imaging area to be diagnosed and N ROI interfaces for the corresponding control area according to the user's selection, wherein N is a plural number of a natural number.

9. The breast cancer diagnosis system according to claim 7, characterized in that: The central control device outputs a diagnosis interface, and the diagnosis interface outputs the chromophore image for displaying the distribution state of the chromophore. The diagnosis interface displays the chromophore image of the diagnosis area generated based on the data collected using the first ROI interface and the chromophore image of the control area generated based on the data collected using the second ROI interface side by side.

10. The breast cancer diagnosis system according to claim 9, characterized in that: The diagnosis interface displays the chromophore image of the diagnosis area and the chromophore image of the control area side by side according to the type of the chromophore.

Images