JP2013212247A - Skin measurement system - Google Patents

Abstract

PROBLEM TO BE SOLVED: To solve the problem that a conventional skin measurement system can only measure a small area and for instance, it is difficult to be used as a reference during foundation application.SOLUTION: A first light source having a peak wavelength from a wavelength of 700 nm to 1,100 nm and a second light source having a peak wavelength from a wavelength of 350 nm to 700 nm irradiate skin of such as a face in order. A signal obtained by measuring reflected light of the skin by irradiating the skin with light from the first light source and a signal obtained by measuring the reflected light of the skin by irradiating the skin with light from the second light source are subjected to a difference computation process. Accordingly, spots and freckles or the like on skin in a large area such as a face can be measured by a relatively inexpensive system.

Description

  The present invention relates to a system for measuring skin components, and more particularly, to a system for exaggerating and displaying skin-derived melanin-derived products and hemoglobin-derived products.

  In order to grasp beauty and health conditions, the state of skin is observed and measured. It is often used on a daily basis to visually measure with a mirror. As a method using a measuring instrument, melanin-derived products such as stains, buckwheat, dullness, bears, or hemoglobin pigment-derived products such as erythema and dermatitis are visually observed or mexameter (collage and A measuring instrument called “Kazaka Co., Ltd.” is used.

  The megger meter is a measuring instrument that measures the amount of melanin and hemoglobin in the skin. In the skin to be evaluated, 568 nm (hereinafter sometimes referred to as “green”) which is green, 660 nm (hereinafter sometimes referred to as “red”) which is red, and 880 nm which is near infrared light. (Hereinafter, referred to as “infrared”), an irradiation unit that irradiates three types of wavelengths, a reflection intensity measurement unit that measures the reflection intensity of reflected light, and the amount of melanin obtained by analyzing the obtained data It is an apparatus comprising a control unit that calculates and displays the amount of hemoglobin.

  FIG. 9 is a graph illustrating the measurement principle of the megger meter. The horizontal direction of the graph indicates the wavelength, and the vertical direction indicates the absorption rate of the wavelength. This graph shows an absorption spectrum 901 for melanin, an absorption spectrum 902 for hemoglobin, and an absorption spectrum 903 for skin.

  In the megger meter, the melanin amount mx and the hemoglobin amount ex can be obtained by Equations 1 and 2.

(Formula 1: Melanin amount)
mx = {500 / log5} × [log {(infrared reflection) / (red reflection)} + log5]
= {500 / log5} × {log (infrared reflection) -log (red reflection)} + 500
(Formula 2: Hemoglobin amount)
ex = {500 / log5} × [log {(red reflection) / (green reflection)} + log5]
= {500 / log5} × {log (red reflection) -log (green reflection)} + 500
The outline of the measurement principle of the meggerometer will be described with reference to FIG. 9 and Equations 1 and 2. Hemoglobin in the blood has almost no absorption in the wavelength range from red to infrared. In contrast, melanin has a large absorption at the red wavelength, but hardly absorbs at the infrared wavelength. Therefore, the amount of melanin can be measured by subtracting the reflection intensity obtained by measurement at the red wavelength from the reflection intensity obtained by measurement at the infrared wavelength.

  Hemoglobin has a large absorption at the green wavelength, but hardly absorbs at the red wavelength. In addition, melanin does not have a very large change in absorption spectrum between the red wavelength and the green wavelength. Therefore, if the difference in the reflection intensity obtained by the measurement at the green wavelength is taken from the reflection intensity obtained by the measurement at the red wavelength, it can be considered that the change between them is caused by hemoglobin as a dominant factor. Because it can, the amount of hemoglobin is determined. Here, the hemoglobin includes both oxygenated hemoglobin and reduced hemoglobin (hereinafter, “hemoglobin” includes both in this specification).

  In this way, the meggameter cannot eliminate the influence of melanin when measuring hemoglobin, so Patent Document 1 discloses a method of analyzing light of 500 to 700 nm by multiple regression analysis.

JP-A-11-299743

  In the method of visually observing the state of the skin, the error tends to increase depending on the observation environment. For example, when a foundation is applied to the face, it tends to be a so-called thick makeup that is applied in a bright environment, and tends to be applied in a dark environment. This is because the foundation transmits a certain amount of visible light. In a bright environment, the product derived from the melanin pigment passes through the foundation so that it can be easily seen and concealed. This is because the product derived from the melanin pigment is difficult to see through the foundation, and is thus applied thinly.

  In addition, the measurement using a megger meter is made not to be affected by the environment under close contact with the skin. For this reason, only a narrow area with a radius of several centimeters can be measured, and since a photodetector is used, it can be output only as one numerical value within the area. For this reason, it is difficult to use a meguzameter when applying a foundation for cosmetic purposes.

  Similarly, the technique disclosed in Patent Document 1 is the same in principle as the megger meter, and is difficult to use because the area that can be measured is small, etc. Also, since the multiple regression analysis is used, the device tends to be complicated. There is a problem that it takes time.

  In addition, when measuring with a megger meter, it is difficult to make up the part because it is in close contact with the skin, and it is difficult to use it for cosmetic purposes because it must be remembered. .

  The present invention is intended to solve such a problem, and provides a skin measurement system that can be used in a wide area such as the entire face.

  The skin measurement system according to the present invention includes a light receiving unit having a plurality of image sensors, a first light source having a peak wavelength from 700 nm to 1100 nm, and a second light source having a peak wavelength different from that of the first light source. Light source, a signal obtained by irradiating the skin with light from the first light source and measuring the reflected light of the skin with the light receiving unit, and a light receiving unit for irradiating the skin with light from the second light source and receiving the reflected light of the skin And an arithmetic processing unit for performing arithmetic processing on the signal obtained by the measurement in (1).

  The second light source may have a peak wavelength from 350 nm to 700 nm.

  In addition, the light source has a third light source having a different peak wavelength from the first light source and the second light source, and is obtained by irradiating the skin with light from the third light source and measuring the reflected light of the skin with the light receiving unit. You may have an arithmetic processing part for arithmetically processing a signal and the signal obtained by irradiating light from the 2nd light source to skin, and measuring the reflected light of skin with a light-receiving part.

  Further, the first light source has a peak wavelength of 800 nm to 1100 nm, the second light source has a peak wavelength of 600 nm to 800 nm, and the third light source has a peak wavelength of 400 nm to 600 nm, and the peak wavelength of each light source may be different.

  Moreover, you may provide the white light source different from a light source.

  Further, at least one of the first light source to the third light source may be composed of two or more and arranged at a rotationally symmetric position around the center of the light receiving unit.

  Further, the light source may be switched between 100 nanoseconds and 10 seconds.

  Moreover, you may provide the display part displayed based on the signal which carried out the arithmetic process.

  The light receiving unit may be a CCD.

  According to the present invention, skin measurement over a wide area such as the entire face can be performed with a relatively inexpensive system. This can be used as a reference when applying the foundation.

It is the figure which showed the skin measurement system of Embodiment 1 of this invention. It is a figure which shows the absorption spectrum of the factor substance which determines the color of skin. It is a figure which shows the absorption spectrum of the factor substance which determines the color of skin. It is the figure which showed the skin measurement system of Embodiment 2 of this invention. It is a figure which shows the absorption spectrum of the factor substance which determines the color of skin. It is a figure which shows the skin measurement system of Example 1 of this invention. It is the figure which showed the mode when a face was displayed using the skin measuring system of Example 1 of this invention. It is a figure which shows the skin measurement system of Example 2 of this invention. It is a graph explaining the measurement principle of a Megzameter.

(Embodiment 1)
FIG. 1 is a diagram showing a skin measurement system according to the first embodiment.

  The skin measurement system 100 according to this embodiment includes a first light source 101, a second light source 102, and a light receiving unit 103. The skin measurement system 100 processes the image measured by the light receiving unit 103 by the first calculation unit 104 and the second calculation unit 105, processes the processed image by the third calculation unit 106, and displays the image. Display on the device 107. A white light source 108 is also provided.

  Here, a case where facial skin is measured will be described as an example.

  First, light is irradiated from the first light source 101 to the face of the measurement subject. The reflected light of the light irradiated on the face is imaged and measured by a light receiving unit 103 composed of a CCD (Charge Coupled Device) having elements arranged in a matrix. The first computing means 104 performs signal processing such as digitization and noise processing on the photographed image signal, and converts it into a first image signal.

  Next, light is irradiated from the second light source 102 to the face of the measurement subject. The irradiated light has a wavelength different from that of the first light source, but it is sufficient that the peak wavelength is different. Although the tails may overlap in the spectrum waveform, it is desirable that they do not overlap in the half-width region of the peak wavelength. The reflected light of the light irradiated on the face is imaged and measured by a light receiving unit 103 composed of a CCD (Charge Coupled Device) having elements arranged in a matrix. The second computing means 105 performs signal processing such as digitization and noise processing on the photographed image signal and converts it into a second image signal.

  The third calculation means 106 performs a difference calculation process on the first image signal and the second image signal. As a result, an image signal obtained by taking the difference between the light having the wavelength emitted from the first light source 101 and the light having the wavelength emitted from the second light source 102 is obtained. At this time, a specific signal of the signal may be emphasized.

  The image signal processed by the third computing means is displayed on the display device 107 and can be visually confirmed by the eye of the measurer. The person to be measured and the person to be measured may be the same person.

  In the image signal obtained by the skin measurement system 100 of the present invention, the melanin pigment-derived product or the hemoglobin pigment-derived product is displayed in an exaggerated manner as compared with the appearance of the face under general white illumination. Hereinafter, the principle will be described.

(Product derived from melanin pigment)
FIG. 2 is a diagram showing an absorption spectrum of a factor substance that determines skin color. Each absorption spectrum is an absorption spectrum of melanin 201, skin 202, and water 203. The wavelength band 204 is ultraviolet light of 350 nm or less, the wavelength band 205 is from 350 to 700 nm ultraviolet light to visible light, and the wavelength band 206 is from 700 to 1100 nm visible light to infrared light (near infrared light). The wavelength band 207 is infrared light (near infrared light) of 1100 nm or more.

The absorption spectrum 201 of melanin has a large absorption of 100 (10 ² ) cm ⁻¹ or more up to near 600 nm, the absorption starts to decrease rapidly in the vicinity of 600 nm, and the absorption becomes almost zero in the vicinity of 1000 nm.

The absorption spectrum 202 of the skin has a large absorption of 100 (10 ² ) cm ⁻¹ or more up to near 300 nm, which is ultraviolet light, and begins to gradually decrease from 300 nm, and is smaller than 100 cm ^{−1 in} visible light. Similarly, the absorption becomes almost zero near 1000 nm.

  The absorption spectrum 203 of water hardly absorbs in ultraviolet light and visible light, and starts to absorb light from around 1100 nm that is infrared light.

  It can be seen from FIG. 2 that if a wavelength band having a large difference in absorption spectrum between melanin and skin is used, the melanin pigment-derived product and the skin (region without the melanin pigment-derived product) can be appropriately separated. In the present invention, the peak wavelength of the wavelength irradiated from the first light source 101 of the skin measurement system 100 is set to the wavelength 206 (700 to 1100 nm), and the peak wavelength of the wavelength irradiated from the second light source 102 is the wavelength 205. (350 to 700 nm). The third computing means 106 performs a difference computation process on the first image signal photographed using the first light source 101 and the second image signal photographed using the second light source 102.

  In the region where the melanin pigment-derived product is present on the skin surface of the face, the second light source having the peak wavelength in the wavelength band 205 has absorption of both melanin and skin, so that the reflected light becomes small. The difference between the intensity of the image signal and the intensity of the second image signal becomes large. On the other hand, in the area where the melanin pigment-derived product does not exist on the skin surface of the face, there is no absorption by melanin and only absorption by the skin, so there is an intensity difference between the image signal between the first image signal and the second image signal. Get smaller.

  As a result, the region where the melanin pigment-derived product exists can be specified, and the display device 107 displays the melanin pigment-derived product in an exaggerated manner. For example, the image signal processed by the third calculation means is displayed such that the luminance is lower (black) as the difference between the first image signal and the second image signal is larger, and the luminance is smaller as the difference is smaller. If displayed so as to be high (white), a region where the melanin pigment-derived product is present is displayed in black, and a region where the melanin pigment-derived product is not present is displayed in white. On the other hand, the image signal processed by the third calculation means is displayed so that the luminance is higher (whiter) as the difference between the first image signal and the second image signal is larger, and the luminance is smaller as the difference is smaller. If displayed to be low (black), the region where the melanin pigment-derived product is present is displayed in white, and the region where the melanin pigment-derived product is not present is displayed in black.

(Hemoglobin pigment-derived product)
FIG. 3 is another diagram showing an absorptivity spectrum of a factor substance that determines the color of the skin. Each absorption spectrum is an absorption spectrum of hemoglobin 301, skin 302, and water 303. The wavelength band 304 is ultraviolet light of 300 nm or less, the wavelength band 305 is from 300 to 400 nm ultraviolet light to visible light, the wavelength band 306 is visible light from 400 to 700 nm, and the wavelength band 307 is from 700 to 700 nm. From visible light of 1100 nm to infrared light (near infrared light), the wavelength band 308 is infrared light (near infrared light) of 1100 nm or more.

The absorption spectrum 301 of hemoglobin ranges from approximately 10 (10 ¹ ) cm ⁻¹ to 100 (10 ² ) cm ⁻¹ up to near 300 nm, and several absorption peaks appear from 300 nm, and the absorption is almost in the vicinity of 700 nm. It becomes zero.

The absorption spectrum 302 of the skin has a large absorption of 100 (10 ² ) cm ⁻¹ or more up to near 300 nm, which is ultraviolet light, and begins to gradually decrease from 300 nm, and is less than 100 cm ^{−1 in the} visible light, and is close to 1000 nm. The absorption becomes almost zero.

  The absorption spectrum 303 of water hardly absorbs in ultraviolet light and visible light, and begins to absorb light from around 1100 nm that is infrared light.

  From FIG. 3, it is possible to appropriately separate the hemoglobin pigment-derived product and the skin (region without the hemoglobin pigment-derived product) by using a wavelength band in which the difference in absorption spectrum between hemoglobin in blood and skin is large. Recognize. In the present invention, the peak wavelength of the wavelength irradiated from the first light source 101 of the skin measurement system 100 is set to the wavelength 307 (700 to 1100 nm), and the peak wavelength of the wavelength irradiated from the second light source 102 is the wavelength 306. (400 to 700 nm). The third computing means 106 performs a difference computation process on the first image signal photographed using the first light source 101 and the second image signal photographed using the second light source 102.

  In the region where the hemoglobin pigment-derived product is present on the skin surface of the face, the second light source having a peak wavelength in the wavelength band 306 has absorption of both hemoglobin and skin, and thus the reflected light becomes small. The difference between the intensity of the image signal and the intensity of the second image signal becomes large. On the other hand, in the region where the product derived from the hemoglobin pigment is not present on the skin surface of the face, there is no absorption by hemoglobin and only absorption by the skin, so there is an intensity difference between the image signals of the first image signal and the second image signal. Get smaller.

  As a result, the region where the hemoglobin pigment-derived product is present can be specified, and the hemoglobin pigment-derived product is exaggerated and displayed on the display device 107. Since the appearance on the display device 107 is the same as that described for the melanin-derived product, the description thereof is omitted.

(Comparison with conventional technology)
Comparison is made between the case of using white light and the case of using light of a specific wavelength as in the present invention. The image signal obtained by the skin measurement system 100 of the present invention is an exaggerated product derived from a melanin pigment and a product derived from a hemoglobin pigment compared to an image signal obtained by irradiating ordinary white light.

The case where a melanin pigment-derived product is measured by the skin measurement system 100 of the present invention will be described. The peak wavelengths of the first light source 101 and the second light source 102 are λ1 and λ2, respectively. _Assuming that the intensities are R _M (λ) and R _S (λ), image signals obtained by the skin measurement system 100 of the present invention are as follows.

First, the reflection intensity (R _M ) in the region where the melanin pigment-derived product exists and the region where the melanin pigment-derived product does not exist, that is, the skin reflection intensity (R _S ) are expressed by the following equations.

(Formula 3: Region where melanin pigment-derived product exists)
R _M (λ1) −R _M (λ2)
(Formula 4 :)
R _S (λ1) −R _S (λ2)
In order to increase the contrast of the image signal, the difference between Expression 3 and Expression 4 should be large, and the numerical value obtained from the following expression should be large.

(Formula 5: Contrast ratio)
(R _S (λ1) −R _S (λ2)) − (R _M (λ1) −R _M (λ2))
On the other hand, in the image signal obtained by irradiating normal white light, the reflection intensity and the melanin pigment-derived generation in the region where the melanin pigment-derived product exists in all light in the visible wavelength region (380 to 780 nm). It is the result of integrating the values in the area where no object exists. That is, an average contrast at all wavelengths in visible light can be obtained.

  (Formula 6: Contrast ratio with white light)

From the above, in the skin measurement system 100 of the present invention, the first light source 101 and the second light source 101 and the second light source have a wavelength (for example, λ1 = 800 to 1000 nm, λ2 = 600 to 700 nm) at which the difference in reflectance between melanin and skin becomes the largest. The peak wavelength of the light source 102 can be set and can be measured using a wavelength with which a difference in the melanin-derived product can be sufficiently obtained, whereas the measurement apparatus described in Patent Document 1 or normal visual confirmation is sufficient. The contrast cannot be taken.

  In addition, the conventional megger meter and the measuring device of Patent Document 1 can measure only a narrow area of skin, and it has been difficult to refer to, for example, when applying a foundation. Also, the photo detector used in the Megzameter can measure only a single data within the area, making it difficult to measure skin over a wide area. However, if the skin measurement system 100 of the present invention is used, the skin can be measured over a wide area such as the entire face with a relatively inexpensive system.

  It is desirable that the half width of the spectrum of the light emitted from the first light source 101 and the second light source 102 is narrow. The reason is that the peak wavelength of each light source is set so that the difference between the reflection intensity of melanin and the skin becomes large, but when the half-value width of each light source becomes wide, the area where the difference in reflection intensity is small is averaged and melanin This is to worsen the skin contrast. Specifically, the spectral half width of each light source is preferably 100 nm or less, and preferably 50 nm or less. As a light source for realizing this, there are an LED (Light Emitting Diode) and an LD (Laser Diode). However, an LD is desirable because of its high price and poor power efficiency within the normal operating power range.

  Besides the LED and LD, a neon lamp (peak wavelength from 640 to 710 nm) can be used as the first light source 101, and a mercury lamp (peak wavelength from 350 nm to 550 nm) can be used as the second light source 102. Since these lamps have a plurality of peak wavelengths, a filter may be attached to reduce the half width. These lamps can be used with either melanin or hemoglobin.

  The peak wavelengths of the first light source 101 and the second light source 102 are desirably set so as not to cover the wavelength band 207 in FIG. 2, that is, the peak wavelength does not exceed 1100 nm. This is because the absorption of water becomes so large that it cannot be ignored at 1100 nm or more, so that the reflection intensity becomes weak and it becomes difficult to detect light in the light receiving section. In addition, the CCD used in the light receiving unit 103 normally has a light receiving sensitivity of up to about 1000 nm, and cannot be photographed even if a long wavelength light source is used. Therefore, it is preferable that the peak wavelength does not become 1100 nm or more.

  The above description is the same for hemoglobin. In the case of hemoglobin, the peak wavelength of the first light source 101 can be set to the wavelength band 307 (700 to 1100 nm), and the peak wavelength of the second light source can be set to the wavelength band 305 (300 to 400 nm). However, since an LED having a peak in the wavelength band 305 is more expensive than an LED (semiconductor light emitting element) having a peak in the wavelength band 306, it is cheaper to use an LED having a peak in the wavelength band 306.

  The skin measurement system 100 of the present invention includes a white light source 108. The white light source 108 includes a white LED. Since Megzameter is used in close contact with the skin, it does not look directly at the light source. Therefore, there is no sense of incongruity in use because it is not seen directly even if green light is applied to the skin. However, in the skin measurement system 100 of the present invention, the light from the light source hits the face, and the light from the light source can be seen at the time of use. However, there is a risk that a sense of incongruity in use may occur. Therefore, the skin measurement system 100 of the present invention uses the white light source 108 and irradiates the white light for a time that does not affect the measurement, thereby eliminating the uncomfortable feeling during use.

  As described above, according to the present invention, skin measurement of a wide area such as the entire face can be performed with a relatively inexpensive system. This can be used as a reference when applying the foundation.

(Embodiment 2)
FIG. 4 shows a skin measurement system according to the second embodiment.

  The skin measurement system 400 according to this embodiment includes three light sources unlike the first embodiment, and performs accurate measurement by performing arithmetic processing using separate light sources for the melanin pigment-derived product and the hemoglobin pigment-derived product. be able to. The measurement mode between the melanin pigment-derived product and the hemoglobin pigment-derived product may be manually switched by the user, or may be switched automatically.

  The skin measurement system 400 includes a first light source 401, a second light source 402, a third light source 403, and a light receiving unit 404. The skin measurement system 400 processes the image measured by the light receiving unit 404 by the first calculation unit 405, the second calculation unit 406, and the third calculation unit 407, and the processed image is subjected to the fourth calculation. The data is processed by means 408 and fifth arithmetic means 409 and displayed on the display device 410. In addition, a white light source 411 is provided.

  The mode for measuring the melanin pigment-derived product will be described.

  First, the face of the measurement subject is irradiated with light from the first light source 401. The reflected light of the light irradiated on the face is imaged and measured by a light receiving unit 404 comprising a CCD having elements arranged in a matrix. The first computing means 405 performs signal processing such as digitization and noise processing on the captured image signal, and converts it into a first image signal.

  Next, the face of the measurement subject is irradiated with light from the second light source 402. The light to be irradiated has a wavelength different from that of the first light source, but the peak wavelength may be different, and the tails may overlap in the spectrum waveform. The reflected light of the light irradiated on the face is imaged and measured by a light receiving unit 403 composed of a CCD having elements arranged in a matrix. The second computing means 406 performs signal processing such as digitization and noise processing on the photographed image signal and converts it into a second image signal.

  The fourth calculation means 408 performs a difference calculation process on the first image signal and the second image signal. As a result, an image signal obtained by taking the difference between the light with the wavelength emitted from the first light source 401 and the light with the wavelength emitted from the second light source 402 is obtained. At this time, a specific signal of the signal may be emphasized.

  The image signal processed by the fourth calculation means is displayed on the display device 410 and can be visually confirmed by the eye of the measurer. The person to be measured and the person to be measured may be the same person.

  A mode for measuring a hemoglobin pigment-derived product will be described.

  First, the face of the person to be measured is irradiated with light from the second light source 402, the reflected light of the face is imaged and measured by the light receiving unit 404, and calculation processing is performed by the second calculation means 406. Next, the face of the person to be measured is irradiated with light from the third light source 403, the reflected light of the face is imaged and measured by the light receiving unit 404, and arithmetic processing is performed by the third arithmetic means 407 to obtain a third image signal. . The fifth calculation means 409 performs a difference calculation process on the second image signal and the third image signal. As a result, an image signal obtained by taking the difference between the light with the wavelength emitted from the second light source 402 and the light with the wavelength emitted from the third light source 403 is obtained.

  In the image signal obtained by the skin measurement system 400 of the present invention, the melanin pigment-derived product or the hemoglobin pigment-derived product is exaggerated and displayed as compared with the appearance of the face under general white illumination.

  FIG. 5 is a diagram showing an absorption spectrum of a factor substance that determines the color of the skin.

  Each absorption spectrum is an absorption spectrum of melanin 501, hemoglobin 502, skin 503, and water 504. The wavelength band 505 is from 400 nm or less ultraviolet light to visible light, the wavelength band 506 is from 400 to 600 nm visible light, and the wavelength band 507 is from 600 to 800 nm visible light to infrared light (near infrared light). The wavelength band 508 is visible light to infrared light (near infrared light) from 800 nm to 1100 nm, and the wavelength band 509 is infrared light (near infrared light) of 1100 nm or more.

The absorption spectrum 501 of melanin has a large absorption of 100 (10 ² ) cm ⁻¹ or more up to near 600 nm, the absorption starts to decrease rapidly in the vicinity of 600 nm, and the absorption becomes almost zero in the vicinity of 1000 nm.

The absorption spectrum 502 of hemoglobin ranges from approximately 10 (10 ¹ ) cm ⁻¹ to 100 (10 ² ) cm ⁻¹ up to near 300 nm, and several absorption peaks appear from 300 nm, and the absorption is almost in the vicinity of 700 nm. It becomes zero.

The absorption spectrum 503 of the skin has a large absorption of 100 (10 ² ) cm ⁻¹ or more up to around 300 nm which is ultraviolet light, starts to decrease gradually from 300 nm, and is smaller than 100 cm ^{−1 in the} visible light, and is close to 1000 nm. The absorption becomes almost zero.

  The absorption spectrum 504 of water has almost no absorption in ultraviolet light and visible light, and begins to absorb light from around 1100 nm that is infrared light.

  In the skin measurement system 400 according to the present embodiment, the peak wavelength of the first light source 401 is the wavelength band 508 (800 to 1100 nm), the peak wavelength of the second light source 402 is the wavelength band 507 (600 to 800 nm), and the third light source. The peak wavelength of 403 is set in the wavelength band 506 (400 to 600 nm).

  In the first embodiment, measurement was performed using two light sources. However, in this embodiment, the melanin pigment-derived product and the hemoglobin pigment-derived product include both the melanin pigment-derived product and the hemoglobin pigment-derived product by using three light sources including light sources having different peak wavelengths. Even in cases, you can make a measurement that identifies which is the cause.

  Specifically, when measuring melanin, the first light source 401 uses a wavelength band 508 (800 to 1100 nm) and the second light source 402 uses a wavelength band 507 (600 to 800 nm). Melanin has almost no absorption in the wavelength band 508 and has a large absorption in the wavelength band 507, particularly 600 to 700 nm. Hemoglobin has almost no absorption in both wavelength bands 507 and 508. Therefore, the amount of melanin can be measured by taking the difference in reflection intensity.

  When measuring hemoglobin, the second light source 402 uses the wavelength band 507 (600 to 800 nm) and the third light source 403 uses the wavelength band 506 (400 to 600 nm). Hemoglobin has almost no absorption in the wavelength band 507, particularly 700 nm or more, and the absorption is large in the wavelength band 506. Melanin does not have a very large change in absorption spectrum in the wavelength band 506 and the wavelength band 507, particularly 700 nm or less. Therefore, the amount of melanin can be measured by taking the difference in reflection intensity.

  As described above, in the present embodiment, not only the melanin pigment-derived product and the hemoglobin pigment-derived product are displayed with emphasis, but also measurement with higher accuracy than in the first embodiment is possible.

  In the embodiment, the wavelength of the light source is indicated by the wavelength band, but light having a wavelength that is far enough to use the difference may be used. Theoretically, it is possible if the peak wavelength is 10 nm or more apart, but it is preferable that the peak wavelength is about 50 nm apart in consideration of the half width of the LED.

  The skin measurement system 400 of the present invention includes a white light source 411. The white light source 411 includes a white LED or the like. As described above, the skin measurement system 411 of the present invention is exposed to light from the light source on the face, which may cause a sense of discomfort during use. Therefore, the skin measurement system 400 of the present invention uses the white light source 411 and irradiates the white light for a time that does not affect the measurement, thereby eliminating the uncomfortable feeling during use.

  Hereinafter, more specific examples will be described.

Example 1
FIG. 6 is a diagram showing a skin measurement system according to Example 1 of the present invention.

  FIG. 6A is a schematic diagram of a skin measurement system 601. The skin measurement system 601 includes a camera unit 602 and a display unit 603, both of which are connected by a cable 604. The skin measurement system 601 uses the camera unit 602 to photograph the skin of a measurement object such as a face, and displays an image processed based on the photographed image on the display unit 603.

  FIG. 6B is a front view of the camera unit 602. The camera unit 602 includes a camera 605 and measurement LEDs 606 to 608. In addition, a white LED 617 is provided.

  The LEDs 606 to 608 are for irradiating an object to be measured such as a face, and are the first to third light sources in the embodiment. For example, the LED 606 that emits near-infrared light, the LED 607 that emits red light, and the green light source. The LED 608 emits light. The white LED 617 is a white light source for eliminating a sense of incongruity during use. These LEDs are arranged so as to surround the camera 605. Thereby, it can avoid that a shadow arises in a to-be-measured object by irradiation from one direction. In order to exert this effect, it is desirable that LEDs of the same color are arranged at rotationally symmetric positions around the center of the camera. Note that the arrangement order is not necessarily as described, and it is not essential that the LEDs are arranged so as to surround the camera, as long as at least one color is provided.

  FIG. 6C is a block diagram inside the camera unit 602. The camera unit 602 includes an LED 607 (having other LEDs, but not shown), a lens 609, a CCD 610, a power supply circuit 611, a control circuit 612, an arithmetic circuit 613, a primary memory 614, a display unit interface 615, and a mode switch 616. Yes.

  The camera 605 takes an image with the CCD 610 as a light receiving unit via the lens 609. It is preferable to use a CCD 610 that can shoot up to a wavelength of about 1000 nm. The LEDs 606 to 608 are turned on / off by the control circuit 612 and the irradiation intensity is controlled. The control may be sequentially switched at predetermined time intervals, or may be performed manually based on the mode changeover switch 616.

  Light is irradiated to the face from one LED among the LEDs 606 to 608, and reflected light of the skin on the face is photographed and measured by the camera 605. Here, the LED 606 is the first light source 401 and has a peak wavelength of 940 nm, which is near infrared light, and a half width of 30 nm, and the LED 607 is the second light source 402, which has a peak wavelength of 700 nm, which is red, and the half width is The LED 608 is the third light source 403 and has a peak wavelength of 525 nm, which is green, and the half width is 30 nm.

  The CCD 610 serving as a light receiving unit of the camera has a large number of imaging pixels, and can measure the skin condition of the face with a resolution corresponding to the number of pixels. The captured image signal is subjected to image processing such as noise filtering by the arithmetic circuit 613 and stored in the primary memory 614. Next, light is emitted from another LED among the LEDs 606 to 608, and the reflected light of the skin of the face is photographed and measured by the camera 605. The captured image signal is subjected to image processing by the arithmetic circuit 613 and stored in the primary memory 614. The two image signals stored in the primary memory 614 are subjected to differential processing by the arithmetic circuit 613. The processed image signal is sent to the display unit 603 via the display unit interface 615. Thereby, an image signal is displayed on the display unit 603 in real time. These operations are desirably performed in a range of 100 ns to 10 s. This is because it is technically difficult to repeat in less than 100 ns because the LED having the fastest response speed among light sources is about 100 ns. On the other hand, if it is longer than 10 s, the face image displayed on the display unit is updated every 10 s, which causes a waiting time when applying makeup while watching the image in real time, which is inconvenient to use. .

  The mode changeover switch 616 can switch between a melanin pigment-derived product confirmation mode and a hemoglobin pigment-derived product confirmation mode according to a user's request. According to the mode desired by the measurer, the control circuit 612 determines which of the LEDs 606 to 608 is to be operated. For example, in the case of the melanin pigment-derived product confirmation mode, the LED 606 and the LED 607 are alternately lit, and in the case of the hemoglobin pigment-derived product confirmation mode, the LED 607 and the LED 608 are alternately lit.

  FIG. 7 is a diagram showing a state when a face is displayed using the skin measurement system of the present embodiment. As shown in FIG. 7A, the display unit 701 of the skin measurement system shows the entire face, and the difference image signal between the first image signal and the second image signal is displayed in a gray scale of white and black. Is done. The melanin pigment-derived product 702 is displayed in an exaggerated manner compared to an image obtained by irradiating with normal white light, so that the melanin pigment-derived product 702 is darkly displayed in black in the region where the melanin pigment-derived product 702 exists. It has become. The eyes, nose, mouth, and the like are also displayed because the reflectance differs from the skin. The foundation or the like can be applied while viewing this image, and the foundation can be applied so that the melanin pigment-derived product is hidden until it disappears from the image of the display device as shown in FIG. According to the present invention, it is possible to apply the foundation while watching the face image as described above, which is very useful.

  In the present embodiment, it is preferable to increase the time during which the white LED 617 is irradiated and shorten the irradiation time of the other LEDs. In particular, the LED 607 and the LED 608 are visible light, and the face is irradiated with red or green, which may give a bad impression to the user. Further, the LED 606 is basically invisible because it is also infrared, but depending on the half-value width, light in the visible light region is also emitted. For this reason, it is desirable that the LEDs 606 to 608 have the minimum necessary lighting time that can be processed by the system. Since the afterimage of the previous image can be seen even if the human eye is switched for about 1/30 seconds, the LED 606 should be switched to the LED 608 at a speed of 1/30 seconds or less, and the LED 617 should be irradiated for the remaining time. Is preferred.

  In this embodiment, the camera unit 602 and the display unit 603 are connected by a cable, but may be connected by wireless communication such as infrared communication or WiFi. In that case, if a battery such as a rechargeable battery, a dry battery, or a solar battery is provided in the camera unit 602, a system that is easy to use can be obtained.

(Example 2)
FIG. 8 is a diagram showing a skin measurement system according to Embodiment 2 of the present invention.

  FIG. 8A is a schematic diagram of a skin measurement system 801. The skin measurement system 801 includes a camera unit 802, a left display unit 803, a right display unit 804, and a mirror 805. The skin measurement system 801 of the present embodiment is a dresser type, and may have a drawer or the like for storing cosmetics as shown in the figure as needed.

  FIG. 8B is an enlarged view of the camera unit 802. A left-side shooting camera 806 and a right-side shooting camera 807 are provided, and these cameras correspond to the left display portion 803 and the right display portion 804, respectively. The LEDs 808 to 811 for irradiation are common in left and right photographing, the LED 808 is near infrared light with a peak wavelength of 940 nm, the LED 809 is red with a peak wavelength of 700 nm, the LED 810 is green with a peak wavelength of 525 nm, and the LED 811 Is a broadband white LED. Since the skin measuring system 801 has a mirror 805, the face in a natural state is projected onto the mirror 805 by irradiating the face with the white LED 811. In the display units 804 and 805, an image in which a melanin pigment-derived product that has been processed in the same manner as in Example 1 is emphasized is displayed. The LEDs 808 to 811 are common to the left and right photographing, but may be arranged separately on the left and right.

  In the present embodiment, it is preferable to lengthen the time that the white LED 811 is radiating and shorten the irradiation time of the other LEDs. In particular, the LED 809 and the LED 810 are visible light, and a face irradiated with red or green is reflected on the mirror, which may give a bad impression to the user. Further, although the LED 808 is basically invisible because it is infrared, depending on the half-value width, light in the visible light region is also emitted. Therefore, it is desirable that the LEDs 808 to 810 have a minimum lighting time that can be processed by the system. Since the afterimage of the previous image can be seen even if the human eye is switched for about 1/30 seconds, the LED 810 should be switched to the LED 810 at a speed of 1/30 seconds or less, and the LED 811 should be irradiated for the remaining time. Is preferred.

  Here, the reflected light of the white LED 811 is captured by the mirror 805, but it may be measured by a photographing camera such as a CCD and projected on a display device.

  The cameras 806 and 807 take images in synchronization with the LEDs, perform image processing, and display them on the display units 803 and 804. If the image is switched about once a second, it can be used practically without any problem. Since the measurement system of this embodiment is the same as that of Embodiment 1, detailed description thereof is omitted.

  In this embodiment, since the left-side shooting camera 806 and the right-side shooting camera 807 are provided, a product derived from melanin pigment or a hemoglobin pigment in an area that cannot be seen from the inner front of the face, for example, under the left and right gills. The derived product can be confirmed, and care such as foundation application can be performed.

  As described above, the skin measurement system of the present invention can be used to measure skin with a wide area such as a face with a simple configuration as described with reference to the embodiments. Therefore, it can be used as a reference for makeup. When visually confirmed, it was difficult to properly apply the foundation based on the amount of ambient light, but using this system makes it possible to apply the foundation appropriately.

  In the embodiment, the face is photographed, but other parts may be used. For example, it can be used for a wide part such as a hand, a leg, and a torso.

  Moreover, it is possible to construct a skin measurement system similar to that of the embodiment by combining an apparatus having a calculation processing unit equipped with a camera such as a smartphone or a personal computer and the light source described in the embodiment.

  The present invention can be used in the field of measuring skin components.

100, 400, 601, 801 Skin measurement system 101, 102, 401, 402, 403, 606, 607, 608, 808, 809, 810 Measurement light source 108, 411, 617, 811 White light source 103, 404, 602, 806 807 Light-receiving part (camera)
104, 105, 106, 405, 406, 407, 408, 409, 613 Arithmetic means (arithmetic circuit)
107, 410, 603, 701, 803, 804 display device

Claims (9)

A light receiving section having a plurality of image sensors;
A first light source having a peak wavelength from 700 nm to 1100 nm;
A second light source of visible light having a peak wavelength different from that of the first light source;
A signal obtained by irradiating the skin with light from the first light source and measuring the reflected light of the skin with the light receiving unit, and a light obtained by irradiating the skin with light from the second light source and measuring the reflected light of the skin with the light receiving unit An arithmetic processing unit for arithmetically processing the signal obtained by
A skin measurement system equipped with.   The skin measurement system according to claim 1, wherein the second light source has a peak wavelength from 350 nm to 700 nm.   It has a third light source having a peak wavelength different from that of the first light source and the second light source, and is obtained by irradiating the skin with light from the third light source and measuring the reflected light of the skin with a light receiving unit. And an arithmetic processing unit for performing arithmetic processing on the signal obtained by irradiating the skin with light from the second light source and measuring the reflected light of the skin with a light receiving unit. Item 10. The skin measurement system according to Item 1.   The first light source has a peak wavelength of 800 nm to 1100 nm, the second light source has a peak wavelength of 600 nm to 800 nm, and the third light source has a peak wavelength of 400 nm to 600 nm, and the peak wavelength of each light source is different. 4. The skin measurement system according to 3.   The skin measurement system according to claim 1, further comprising a white light source different from the light source.   The skin measurement system according to any one of claims 1 to 5, wherein at least one of the light sources is composed of two or more light sources and is disposed at a rotationally symmetric position around the center of the light receiving unit.   7. The skin measurement system according to claim 1, wherein the light source is switched between 100 nanoseconds and 10 seconds.   The skin measurement system according to claim 1, further comprising a display unit configured to display based on the arithmetically processed signal. 9. The skin measurement system according to claim 1, wherein the light receiving unit is made of a CCD.