KR102130309B1 - Measuring device for condition of skin - Google Patents

Abstract

Disclosed is a skin condition diagnosis device.
Disclosed herein is an apparatus for diagnosing roughness using two types, the first of which is to use a difference in the amount of light reflected from a sample when a plurality of lights irradiate the sample. The second is to monitor whether or not to recognize the applied stimulus.
Through this, the condition of the skin can be objectively measured.

Description

Skin condition measuring device {MEASURING DEVICE FOR CONDITION OF SKIN}

The present technology relates to a measuring device capable of diagnosing and digitizing a skin condition and outputting it.

Skin acts as a protective film that forms the outside of the human body.

The skin prevents the penetration of harmful organisms such as moisture and bacteria into the human body and regulates body temperature. If the skin serving as the protective film is damaged, the human body is not protected and is exposed to various diseases. Therefore, it is very important for the human body that the skin is not damaged.

In general, stylus, optical sectioning and optical interferometry are used to measure the surface roughness of an object.

The stylus type is a method of measuring the roughness of an object by converting minute changes in the stylus into electrical signals by moving the stylus on the surface of the object to be measured. However, the stylus type is a method that is measured by contact between the stylus and an object.

The optical cutting type is a method in which light is irradiated in a certain direction to the measurement surface, and the optically cut surface is observed with a microscope at the reflected optical axis, and the optical wave interference type is caused by the overlap of light reflected by the reference reflective surface and the measured surface. This is a method of measuring the surface roughness by expanding the generated light wave interference pattern with a microscope.

Assuming that these methods are applied to the measurement of the roughness of the skin, the photo-cutting type has a problem of taking a skin sample, and the light wave interference type can be used only for a part of the skin where light is well reflected, and above all, it is sensitive to vibration. There is a problem that a large error occurs even in fine vibration.

In addition, the biggest problem of the above two methods is the method that relies on the visual observation of the examiner, so the subjectivity is intervened, so the objectivity of the measured result is lacking, and it is difficult to apply to the skin.

It will be appreciated that accurate diagnosis must be preceded in order for correct treatment to be performed.

Domestic registered patent registration number "10-1791927 "Method and device for estimating skin surface roughness for cognitive-based haptic feedback device (METHOD AND APPARATUS FOR ESTIMATING ROUGHNESS OF SKIN SURFACE FOR HAPTIC FEEDBACK APPARATUS BASED ON PERCEPTUAL ANALYSIS" Domestic Published Patent Application No. "10-1997-0027177" "The roughness measurement device and method of surface."

An object of the present invention is to provide an apparatus for diagnosing a skin condition that can accurately and objectively measure the roughness or sensitivity of the skin.

In addition, an object of the present invention is to provide an apparatus for diagnosing a skin condition capable of increasing the symptoms of diabetic peripheral neuropathy or pressure sores by measuring moisture, oil, and moisture of the skin.

The technical problems to be achieved by the present invention are not limited to the technical problems mentioned above, and other technical problems not mentioned can be clearly understood by a person having ordinary knowledge in the technical field to which the present invention belongs from the following description. will be.

The skin condition measuring device according to the present invention includes: a housing including an opening portion in contact with the specimen on one side; a reference light disposed in a position corresponding to the opening portion in the interior of the housing to irradiate light at a position perpendicular to the specimen, perpendicular to the specimen Each of the reflected lights is received when the reference light and the reference light and the calibration light are irradiated toward the specimen and have an angle set with the reference light so as to irradiate light at an angle other than the reference light. Measures the roughness calculation unit and the EEG to calculate the roughness of the sample by calculating the difference in light intensity, applies current to the sample according to a predetermined step, and detects the corresponding EEG corresponding to the stimulation of the current to the EEG measured. It includes a sensitivity calculation unit for calculating the sensitivity of the sample corresponding to the intensity of the current.

Here, the housing is formed to include at least one reference point and a symmetry point having an angle set at the reference point and disposed at a symmetrical position, wherein the reference point is arranged with a CCD camera receiving the reference light and reflected light, and the symmetry point Characterized in that the correction lighting is arranged.

Here, the symmetry point is characterized in that a plurality of the plurality of layers are formed along the circumference of the housing.

Here, the roughness calculation unit is connected to the reference lighting, the calibration lighting, and the CCD camera to operate the reference lighting and the calibration lighting in a predetermined order and calculate the difference in light intensity of the light received by the CCD camera to determine the roughness of the specimen. It includes a control unit for calculating.

Here, the sensitivity calculation unit is installed adjacent to the opening, the electroencephalography detection unit for detecting the contact pad and the electroencephalogram that comes into contact with the specimen, and the step-by-step current is applied to the contact pad and the contact pad and connected to the electroencephalography detection unit It includes a control unit for detecting the corresponding brain wave corresponding to the applied current.

Here, the stepwise applied current includes an applied area to which the current is applied and an unlicensed area to which the current is applied, and a ratio occupied by the unlicensed area is not less than 70%.

Here, the current applied in any one of the stepwise applied current is characterized in that the current of the same intensity is applied a plurality of times.

Here, the control unit is characterized in that to correct the intensity of the brainwaves measured by dividing and summing the brainwaves measured while the current of any one step is applied at equal intervals.

Since the present invention measures the roughness of the skin by detecting the light intensity of the lighting and the brain waves reacting to the applied current, the objectivity is guaranteed, and the roughness of the skin can be accurately measured.

In addition, the present invention can measure pressure sores and edema of the skin.

1 shows a state in which a skin condition diagnosis device according to the present invention is installed in a subject.
2 is a block diagram showing each configuration of the skin condition diagnosis apparatus according to the present invention.
Figure 3a is a cross-sectional view showing an embodiment of the skin condition diagnosis device of the present invention, Figure 3b is a cross-sectional view showing another embodiment of the skin condition diagnosis device of the present invention, Figure 3c is a skin condition diagnosis device of the present invention Another embodiment is an enlarged view of a group of correction lights.
Figure 4 shows the contents of configuring the steps according to the operation of the current application unit of the skin condition diagnosis device of the present invention.
FIG. 5 shows a preferred embodiment in which a corresponding brain wave is detected when the current application unit of the skin condition diagnosis apparatus according to the present invention is operated.
Figure 6 shows a preferred embodiment of the amplification operation of the skin condition diagnosis apparatus of the present invention.

Hereinafter, an embodiment of the present invention will be described in detail through exemplary drawings. However, it is not intended to limit the scope of the present invention.

It should be noted that in adding reference numerals to the components of each drawing, the same components have the same reference numerals as possible even though they are displayed on different drawings. In addition, in describing the present invention, when it is determined that detailed descriptions of related well-known structures or functions may obscure the subject matter of the present invention, detailed descriptions thereof will be omitted.

In addition, the size or shape of components shown in the drawings may be exaggerated for clarity and convenience of description. In addition, terms specifically defined in consideration of the configuration and operation of the present invention are only for describing the embodiments of the present invention, and do not limit the scope of the present invention.

Throughout the specification, when a part “includes” a certain component, it means that the component may further include other components, not to exclude other components, unless otherwise stated. In addition, terms such as “…unit”, “…group”, “module”, and “device” described in the specification mean a unit that processes at least one function or operation, which is implemented by a combination of hardware and/or software. Can be.

1 shows a state in which a skin condition diagnosis device according to the present invention is installed in a subject.

2 is a block diagram showing each configuration of the skin condition diagnosis apparatus according to the present invention.

Figure 3a is a cross-sectional view showing an embodiment of a skin condition diagnosis device of the present invention.

The skin condition diagnosis apparatus 1 according to the present invention includes a housing 900, a roughness calculation unit, and a sensitivity calculation unit.

The housing 900 has a set shape and is formed. Since the housing 900 has a set shape, a space having a set size is formed therein. In addition, the housing 900 includes an opening that is open on one side. The opening portion of the housing 900 is in contact with the specimen (eg, the human skin). Since the opening portion of the housing 900 is in contact with the specimen, the interior space of the housing 900 may be closed.

Since the skin condition diagnosis apparatus 1 according to the present invention measures the roughness of a specimen using light of illumination, light should not be incident from the outside. In addition, the interior of the housing 900 should not reflect the reflected light again. Therefore, the interior of the housing 900 is preferably coated with a material that absorbs reflected light. This also applies to the exterior of the housing 900.

It will be apparent that the housing 900 itself may be made of a material that blocks light, rather than being coated with a material that absorbs reflected light in the housing 900 of the present invention.

It is a basic idea that the roughness calculation unit measures the roughness of the specimen by using the difference in the luminosities of the lights emitted at different positions on the specimen and reflecting the light. Several things have to be considered for this idea to be implemented.

One of several factors to consider is the shape of the skin. Skin may be deformed over time, wounds may occur, and pores may be deformed. In other words, the skin does not remain flat.

In the skin, an acid (Profile Peak) is formed, and a bone (Profile Valley) is formed. If the skin is checked in detail, it may protrude from the reference point in the shape of an equilateral triangle, may protrude from the reference point in a circular shape, or may be recessed in the reference point in a rectangular shape.

The shape of the skin may have a different amount of reflecting incident light. Therefore, the illumination is preferably composed of three to irradiate light in a triangular shape. It will be preferable that one illumination is composed of illumination that is incident perpendicularly to the specimen, and the other two illuminations are illumination that enters the specimen from the side. Since the lighting should be installed in the interior space of the housing 900, a space in which such lights are arranged will have to be provided.

Therefore, the skin condition diagnosis device 1 of the present invention is preferably formed to have a reference point and a symmetric point. In one example, this shape will be conical. That is, when the housing 900 is formed in a conical shape as shown in FIG. 3A, a plurality of symmetrical points may be formed at a position spaced apart from one reference point and the reference point.

Here, it will be appreciated that the shape of the housing 900 is not limited to a conical shape. That is, when the position where the light can be installed to emit light perpendicular to the specimen is formed, and the position where the light can be installed to emit light from the side is formed, the shape of the housing will not be a problem. Hereinafter, for convenience of description, the shape of the housing 900 is assumed to be conical and will be described.

The roughness calculation unit includes a reference illumination 100, a correction illumination 200, a CCD camera 300, a roughness measurement unit 830, and a reference DB 860. The reference lighting 100 is disposed at a reference point of the housing 900. That is, the light emitted by the reference lighting 100 is reflected after being incident perpendicularly to the sample. It should be noted that, for convenience, the term “vertical” is expressed here, but also includes an angle that is not exactly 90 degrees.

The correction light 200 is disposed at the symmetry point of the housing 900. It is preferable that at least two or more correction lights 200 are disposed. Here, the symmetry point is preferably disposed at a position symmetrical at the same height with respect to the opening.

The reason is that the correction light 200 emits light so that the light intensity of the reflected light is not affected by the distance between the sample and the correction light 200 by injecting light into the sample.

If the distance between the sample and the calibration light 200 is the same, the difference in light intensity reflected from the sample and incident on the CCD camera 300 is most likely due to other factors such as the shape and color of the surface of the sample. This is because it is highly unlikely to be caused by the difference between the distance between the calibration light 200 and the specimen.

The CCD camera 300 detects the light reflected by the sample when the reference light 100 and the corrected light 200 emit light. The CCD camera 300 generates a charge in proportion to the intensity (quantity) of light received by being reflected on a sample, and is a camera that reproduces an image by measuring the generated charge amount. The image of the camera is output through the display 700 so that the inspector can visually confirm.

The CCD camera 300 is preferably disposed at a reference point. That is, it is preferable to be installed adjacent to the reference lighting (100). More precisely, the CCD camera 300 is preferably installed in the reference housing 910.

The reference housing 910 may be formed in a hexagonal shape in cross section as can be seen in FIG. 3A. The shape of the reference housing 910 is formed to be the same as the shape formed when the cross section of the hexagon is rotated 360 degrees with respect to the longitudinal axis. The reference housing 910 formed as described above is formed in a symmetrical shape based on the center line.

A circular through-hole 920 is formed in the center of the reference housing 910 along the longitudinal direction.

For convenience of description, the shape of the reference housing 910 based on the center will be referred to as an upper reference portion 911, and a lower portion referred to as a lower reference portion 912. It will be appreciated that the through portion 920 is formed to penetrate the upper reference portion 911 and the lower reference portion 912.

A CCD camera 300 is disposed in the through-hole portion 920 of the upper reference portion 911. The position in which the CCD camera 300 is disposed does not exceed the upper reference portion 911 and is not disposed in the lower reference portion 912. The reference lighting 100 is disposed under the lower reference portion 912. More precisely, the reference lighting 100 is disposed around the through-hole 920 in the lower portion of the lower reference portion 912.

As described above, the reference illumination 100 is disposed under the lower reference unit 912, and the CCD camera 300 is disposed in the through portion 920 of the upper reference unit 911, so that the reference illumination 100 emits light. The incident on the CCD camera 300 can be minimized.

The controller 800 may calculate the roughness of the sample by using the difference between the luminosities of the reference illumination 100 and the correction illumination 200 in the CCD camera 300. More precisely, the roughness measurement unit 830 of the control unit 800 performs this.

For convenience of description, this will be described through an embodiment of the present invention of FIG. 3A. In FIG. 3A, the correction light 200 on the left side will be referred to as the first correction light 200a, and the correction light 200 on the right side will be referred to as the second correction light 200b.

In the present invention, when measuring the roughness of a specimen, the color of the specimen (e.g., spots, spots, coloring, etc.) formed on the specimen, which affects the reflected light, and the roughness of the specimen according to the shape (mountain or bone) of the specimen In order to eliminate the influence on the light intensity difference between the reference illumination 100 and the correction illumination 200 is calculated.

This can be performed according to the first embodiment as follows.

The skin condition diagnosis device 1 according to the present invention is installed on the wrist of the subject. And the reference lighting 100 is operated for a predetermined time. The preset time may be 3 seconds as an example. While the reference lighting 100 is operating, the first compensation lighting 200a and the second compensation lighting 200b are not operated. While the reference lighting 100 is operating, the CCD camera 300 stores light reflected from the skin of the subject's wrist. When 3 seconds have elapsed, the reference lighting 100 stops operation. Then, after 2 seconds elapse, the first compensation light 200a is operated for 3 seconds. The CCD camera 300 stores the light reflected from the skin of the subject's wrist while the first correction light 200a is operated. When 3 seconds have elapsed, the operation of the first correction light 200a is stopped. This operation is similar to the second correction light 200b.

The roughness measurement unit 830 according to the first embodiment measures the roughness of the subject's skin through the following correction equation 1.

Correction formula 1

Here, i = 1 to n is a natural number, which means a predetermined number of pixels, α means the light intensity incident on the CCD camera 300 when the reference light 100 is operated, and β is the first correction light 200a. ) Indicates the light intensity incident on the CCD camera 300 during operation, and γ means the light intensity incident on the CCD camera 300 when the second correction light 200b is operated.

In the correction formula 1, the absolute value of the difference between the luminance of the light reflected from the sample when the reference light 100 is operated and the luminance of the light reflected from the sample when the first compensation light 200a is operated and the reference light 100 is operated This is a method of performing correction by summing the absolute value of the difference between the luminance of light reflected from the specimen and the luminance of the light reflected from the specimen when the second correction light 200b is in operation. Since the first compensation light 200a and the second compensation light 200b emit light at a position symmetrical with respect to the sample, the difference in light intensity according to the distance can be corrected.

In addition, the light intensity of the first compensation light 200a and the second compensation light 200b, which emit light from both sides, is calculated from the light intensity of the reference light 100, which emits light from the vertical, based on the specimen. It can reduce the error of the luminous intensity.

K is a constant determined based on the standard roughness data stored in the reference DB 860. In the standard roughness data, information on the sample to be sampled is stored. Since humans have various personalities, the color and roughness of the skin are very different. Therefore, it is necessary to make corrections based on the sample in order to quantify the roughness.

As an example, if the blackness of the skin color is expressed as a numerical value, light emitted with the same luminance on the skin of 8 people and 5 people will be reflected and the difference in luminance received by the CCD camera 300 will occur. In addition, it is natural that the amount of light reflected from the non-specified sample will be different if a wound is present on the skin (specimen) to be measured.

K is a constant for correcting this. Therefore, the roughness measurement unit 830 determines the K to correct the difference from the sample to be measured based on the standard roughness data, and performs an operation for calculating it.

In addition, although α was described above as one reference light 100, it may mean the average value of the light intensity incident on the CCD camera 300 after the plurality of reference lights 100 are sequentially operated.

In the foregoing, it has been described that a plurality of reference lights 100 may be installed on the lower side of the reference housing 910 based on the through-hole 920. This will be explained through FIG. 3A.

Four reference lights 100 may be present. For example, the reference lighting 100 may be operated in a clockwise direction. That is, the reference light 100 at 12 o'clock can be operated for 3 seconds, and then, after the operation is stopped, the reference light 100 at 3 o'clock can be operated for 3 seconds. When operated as described above, four luminosity values will be input to one pixel in the CCD camera 300. The roughness measurement unit 830 calculates the average. The average value determined by the roughness measurement unit 830 is determined as α.

3B is a cross-sectional view showing another embodiment of the skin condition diagnosis device of the present invention, and FIG. 3C is an enlarged view of a group of correction lights in another embodiment of the skin condition diagnosis device of the present invention.

The skin condition diagnosis apparatus 1 according to the second embodiment of the present invention may be provided with a plurality of correction lights 200 at intervals set along the length direction. As can be seen in FIG. 3B, when the plurality of correction lights 200 extend in the vertical direction from the opening, a plurality of correction lights 200 are disposed in the same position when the virtual lines intersecting the virtual lines extend. have. For convenience of explanation, the correction lights 200 in the same position will be named in the same order as the first compensation light group 210 to the second compensation light group 220 from the position close to the opening to the distant position. (In FIG. 3B, the first correction light group 210 to the fifth correction light group 250 are illustrated, but it is natural that the number is not limited to this number.)

The operation sequence of the skin condition diagnosis apparatus 1 according to the second embodiment is not different from the first embodiment. That is, the reference lighting 100 is operated for a predetermined period of time, and then each of the corrected lighting groups is operated in order. That is, the reference lighting 100 according to the second embodiment is operated for 3 seconds, and after the operation is finished, the first correction lighting group 210 is operated for 8 seconds, the operation ends, and the first correction lighting group is again performed. This is how the 220 is operated for 8 seconds.

Here, each group of correction lights 200 is composed of a first correction light 200a and a second correction light 200b. The operation of the first correction lighting group 210 described above for 8 seconds is performed while the first correction lighting 200a is operated for 3 seconds, 2 seconds after the operation is completed, and the second correction lighting 200b is operated. Because. However, it is natural that the time at which each of the correction lights 200 is operated and the time at which they are not operated may be changed.

The roughness measurement unit 830 calculates the roughness of the sample through the following equation.

Correction 2

The same reference numerals in the correction formula 2 and the correction formula 1 described above indicate the same meaning. Therefore, if the difference is explained, k = 1 to n is a natural number, and k represents an operation when the k-th correction light 200 group is operated. That is, when k = 1, the operation between the reference lighting 100 and the first correction lighting group 210 is calculated, and when k = 2, the operation between the reference lighting 100 and the first correction lighting group 220 is calculated. It was calculated.

Since k is the same as in the first embodiment, it will be omitted below.

Additionally, the skin condition diagnosis apparatus 1 according to the first embodiment and the skin condition diagnosis apparatus 1 according to the second embodiment may have a plurality of correction lights 200 formed along the circumference of the housing 900.

Previously, in the first and second embodiments, the correction lighting 200 was described on the basis of the first compensation lighting 200a and the second compensation lighting 200b. The correction lighting 200 of may be arranged.

Since the housing 900 is formed in a cylindrical shape, the first compensation light 200a to the nth compensation light 200 may be installed along the circumference of the circle.

For example, as shown in FIG. 3C, six correction lights 200 may be installed, and the operation of the correction lights 200 may include a first compensation light 200a, a second compensation light 200b, and a clockwise direction. The third compensation light 200c, the fourth compensation light 200d, the fifth compensation light 200e, and the sixth compensation light 200f may be sequentially operated.

In this case, when the reference illumination 100 is operated, the roughness measurement unit 830 sequentially operates the first correction illumination 200a to the sixth correction illumination 200f at the light intensity incident to the CCD camera 300. The difference in light intensity incident on the CCD camera 300 is calculated.

In this case, the correction equation 3 performed by the roughness measurement unit 830 is as follows.

Correction formula 3

In the correction formula 3, the same reference numerals as the correction formula 1 have the same meaning. Δ where the difference is generated means the light intensity incident on the CCD camera 300 when the third compensation light 200c is operated, and ζ is the light intensity incident on the CCD camera 300 when the fourth compensation light 200d is operated. Means, η is the light intensity incident on the CCD camera 300 when the fifth compensation light 200e is in operation, and θ is the light intensity incident on the CCD camera 300 when the sixth compensation light 200d is in operation. Means

Meanwhile, the roughness measurement unit 830 may calculate the roughness of the sample through the average calculation correction formula without using the above-described correction formulas 1, 2, and 3.

The average calculation correction formula is as follows.

Average calculation correction formula

In the above average calculation correction equation, the same reference numerals as in the above-described correction formula 1 have the same meaning.

In the above equation, the average α is the average light intensity of the light incident on the CCD camera 300 when the reference light 100 is operated, based on pixels. The average β is the average of the light intensity incident on the CCD camera 300 when the first compensation light 200a is operated, and the average γ is the average of the pixels when the second compensation light 200b is operated.

If the roughness of the sample to be measured is average, the result obtained will be 0; otherwise, a non-zero number will be obtained. Since this method is implemented through information obtained from a sample, there is an advantage in that standard roughness data stored in the reference DB 860 is not required.

Meanwhile, the condition of the skin is also affected by the thickness of the skin. The thickness of the skin affects the sensitivity of the skin. If this sensitivity is reflected when measuring the condition of the skin, a more accurate skin condition can be diagnosed.

However, in order to measure the condition of the objective skin, the subjectivity of the tester should not be reflected. The subject is not reflected and the best way to quantify the roughness of the skin according to the sensitivity of the skin is to use an EEG.

EEG is measured whenever the brain is active. EEG is a measure of brain activity, so if a stimulus is applied to the sample and the stimulus is recognized, the EEG will change accordingly. This is because the brain recognizes the stimulus and performs electrical activity. If this principle is used, it will be possible to measure the sensitivity of the sample and accurately measure the state of the surface of the sample.

The sensitivity calculation unit of the skin condition diagnosis apparatus 1 according to the present invention includes a contact pad 600, an EEG measurement pad 500, a sensitivity measurement unit 840, an EEG detection unit 870, and a current application unit 810. Here, the sensitivity calculation unit may additionally include a moisture measurement unit 400 and a moisture degree calculation unit 820.

Before operating the sensitivity calculator, the subject must remain stable with his eyes closed. This is because it is good to observe that the measured brain wave does not fluctuate in order to detect the corresponding brain wave observed in response to the stimulus. In addition, the brain waves are changed in response to all movements of the subject. This is because, for example, it changes with the blinking of the eyes or the movement of the head.

In addition, it is preferable to operate the sensitivity calculation unit after operating the roughness calculation unit. This is because a difference occurs in the amount by which the sample is contracted and reflected by the stimulus applied to the sample by the sensitivity operator. Therefore, it is preferable to operate the sensitivity calculation unit after operating the roughness calculation unit.

If it is inevitable to operate the sensitivity operator, it is preferable to operate the roughness operator after sufficient time has elapsed after the sensitivity operator is operated.

The EEG pad 500 is installed and fixed to the subject's head. The EEG measuring pad 500 is connected to the control unit 800. The EEG detection unit 870 of the control unit 800 detects the EEG corresponding to the applied stimulus while detecting the EEG of the subject on which the EEG measurement pad 500 is installed. Corresponding EEG detection will be described in detail later.

The contact pad 600 is installed in the housing 900. The contact pad 600 is installed adjacent to the opening of the housing 900. The contact pad 600 is preferably installed between the opening and the calibration light 200 inside the housing 900. Since the contact pad 600 is disposed in the above position, the contact pad 600 does not interfere with the light emitted by the calibration light 200 reaching the sample.

Since the contact pad 600 needs to apply a current to the sample, it is installed to contact at least the sample. That is, when the subject positions the cuff close to the opening, the contact pad 600 naturally contacts the cuff (sample). The contact pad 600 is connected to the current applying unit 810 to apply current according to the signal of the current applying unit 810.

Figure 4 shows the contents of configuring the steps according to the operation of the current application unit of the skin condition diagnosis device of the present invention.

The current applying unit 810 applies current according to a predetermined step. The step means to apply the same current for a set period. The current applying unit 810 applies current from the first step to the nth step. As the step progresses, the current applying unit 810 applies a current of strong intensity.

The step consists of an authorized area and an unlicensed area, and the applied area and the unlicensed area are repeated. The important thing here is that the time of the applied area and the unlicensed area should be the same for each step, and the time of the unlicensed area is preferably set to be longer than the time of the applied area. It is preferable that the time in the non-annotated area is set to be overwhelmingly longer than the applied area. Preferably, it is desirable to obtain a value greater than 70 by dividing the time in the non-available region by the time in the applied region and multiplying by 100.

This will be described with reference to FIG. 4.

For example, it is assumed that each step is composed of 10 seconds, and there is a 1 second pause between each step and the step. Here, it will be assumed that the subject is in a state in which there is no element that interferes with recognizing the stimulus because there is no separate pain.

The current applying unit 810 outputs the first applying signal for 0.5 seconds in the first step, stops for 1.5 seconds, then outputs the first applying signal again, and repeats stopping for 1.5 seconds. Repeat this 5 times. When the first application signal is applied, the contact pad 600 applies a current of 2 mA, and the first application signal is repeated 5 times, so 5 mA is applied 5 times. During this, the EEG detection unit 870 continuously detects the EEG.

If a corresponding brain wave is not detected in the brain wave of the subject to be measured even when a current of 2 mA is applied, the process proceeds to the next step.

In the second step, the current applying unit 810 repeatedly outputs the second applying signal and stops. Here, the time for outputting the second applied signal and the time for stopping are the same as in the first step. However, the current applied is stronger. That is, when the second applied signal is output, a current of 4mA is applied. This operation is repeated until the EEG sensing unit 870 detects the corresponding EEG.

Then, if the EEG sensor 870 detects the corresponding EEG while the current applying unit 810 outputs the fifth applying signal in step 5, the sensitivity measuring unit 840 outputs roughness information corresponding to the fifth step. .

FIG. 5 shows a preferred embodiment in which a corresponding brain wave is detected when the current application unit of the skin condition diagnosis apparatus according to the present invention is operated.

As described above, the current applying operation and stopping of the current pattern of the current application unit 810 are to make it easier to detect the corresponding EEG. EEG changes do not occur simultaneously with stimulation. It is difficult to observe with the naked eye, but after the stimulus is applied and a minute time has elapsed, the corresponding EEG is observed in the EEG. As an example, after the stimulus is applied, the corresponding EEG is detected about 0.2 seconds to 0.8 seconds later.

Therefore, if a current is applied in a constant pattern, it is possible to easily derive a corresponding EEG if the EEG is detected after a predetermined time has elapsed based on the time at which the current was applied.

That is, referring to FIG. 5, if the current applying unit 810 outputs the applied signals at 0, 1t, 2t, and 3t times, the corresponding EEG is observed at T, 1t + T, 2t + T, 3t + T This is high. The sensitivity measuring unit 840 has a high probability of detecting the corresponding EEG if the current applying unit 810 intensively observes the EEG at a position where a set time has elapsed since the application signal was output as described above.

In addition, in the foregoing, the current application unit 810 has been described as an example of outputting the application signal 5 times, but it is not limited thereto, and it will be understood that it can be applied multiple times. That is, the current application unit 810 may output an application signal over 30 times. However, it will be appreciated that the number of times the current is applied can be adjusted according to the user.

Figure 6 shows a preferred embodiment of the amplification operation of the skin condition diagnosis apparatus of the present invention.

Since the EEG draws an irregular waveform, the corresponding EEG may not be detected even if the subject is observed in a stable state emotion. In order to prevent this, the sensitivity measurement unit 840 amplifies the EEG measured by the EEG detection unit 870. The amplification operation is as follows.

The sensitivity measurement unit 840 cuts the EEG graph measured during each step by the reference time to generate a plurality of EEG graphs and performs summing operations.

6, the sensitivity measuring unit 840 cuts based on the reference time t. If the current applying unit 810 has applied the current 30 times, the cut EEG graph will be 30.

Thereafter, the sensitivity measurement unit 840 sums 30 cut EEG graphs with the first and the end coinciding. That is, it is a method of matching 0 of the first EEG graph and t of the second EEG graph among the cut EEG graphs, and matching t of the first EEG graph and 2t of the second EEG graph. This is done on all of the truncated EEG graphs. Then an EEG graph will be generated.

EEG is formed as an irregular waveform. Therefore, if the sensitivity measurement unit 840 performs amplification operation as described above, if the irregular brain waves are summed up, the value will converge to zero. But the corresponding EEG is not. It always draws a similar type of graph at the same location, so as it adds up, it will amplify.

When the sensitivity measurement unit 840 performs the amplification operation, the corresponding EEG will be amplified and easier to detect. When the corresponding EEG is sensed, the sensitivity measurement unit 840 outputs a sensitivity value corresponding to the current of the stage at which the corresponding EEG is sensed.

Meanwhile, the moisture measurement unit 400 is installed outside the housing 900. If the sample contains too much moisture, it is very important to determine whether it contains the average moisture by measuring the moisture before applying the current because the data obtained by applying the current is error data. Therefore, it is desirable to measure the moisture content of the sample for the sensitivity calculator to operate.

The moisture measuring unit 400 is preferably installed to be in contact with the sample when the sample is located in the opening like the contact pad 600. The reason why the moisture measurement unit 400 is installed on the outside of the housing 900 is that when installed inside, the moisture of the sample itself evaporates to increase the moisture level inside the housing 900. The moisture measuring unit 400 applies a high frequency current, and then measures the impedance.

The moisture conduction calculator 820 acquires the applied high frequency current and the measured impedance to measure the amount of moisture corresponding to the impedance. When the measured moisture level is higher than the preset warning value, it is output to the display 700 and evaporates moisture in the sample, and then outputs a warning signal to operate the sensitivity calculator. If the moisture level is not higher than the warning value, a normal signal of normal is output to the display 700. After that, the sensitivity operation unit is operated.

The display 700 is connected to the control unit 800 and displays information on which the control unit 800 operates. The image output on the display 700 is, for example, a real-time EEG detected by the EEG sensing unit 870, an intensity of a current applied by the current applying unit 810, a current step, or whether a corresponding EEG is detected.

When the roughness calculation unit and the sensitivity calculation unit respectively detect the roughness and sensitivity of the sample, the comprehensive determination unit 850 outputs it as a numerical value.

In addition, the skin condition diagnosis apparatus 1 according to the present invention includes an age calculation unit 880 and an edema measurement unit 1000. The age calculation unit 1000 calculates the age of the skin by comparing predetermined data through the roughness of the skin measured by the roughness calculation unit and the moistness of the skin measured by the contact pad 600.

That is, as an example, the age calculation unit 880 stores preset data from 1 year to 100 years based on the roughness of the skin and the moisture level of the skin (moist). For example, the numerical value output by the roughness calculation unit is 7 It is said that when the skin has a moisture content of 30%, the matching age is data of age A.

Based on this, the age calculation unit 880 measures the impedance of the skin through the contact pad 600 and the numerical value output by the roughness calculation unit and outputs the age based on the moisture content (moistness) of the skin. The age output by the age calculator 880 may be output to the display 700 and visually confirmed.

The edema measurement unit 1000 is formed in the housing 900. The edema measuring unit 1000 is preferably formed of a soft material to minimize irritation to the skin. The edema measurement unit 1000 is formed to protrude. The edema measurement unit 1000 is installed adjacent to the opening in contact with the skin in the housing 900. The edema measuring unit 1000 measures pressure when the housing 900 comes into contact with the skin so that the housing 900 becomes light-shielding and outputs a pressure value when the housing 900 comes into contact with the light-shielding.

That is, when the housing 900 is in close contact with the skin and is shielded through the CCD camera 300, the degree of skin softness is calculated and output using the pressure value applied to the edema measurement unit 1000 and output.

Here, the edema measurement unit 1000 is not shown, but is connected to a small motor and actuator to move up and down in the vertical direction. The skin condition diagnosis apparatus according to the present invention through the edema measuring unit 1000 may examine edema and the like.

The operation method of the principle of the edema measurement unit 1000 is as follows.

A pressure measuring sensor 1100 is installed under the housing 900. When the housing 900 comes into contact with the skin, the pressure measurement sensor 1100 measures the pressure value. In addition, the edema measurement unit 1000 is provided with a sensor capable of pressure measurement.

When the edema measurement unit 1000 comes into contact with the skin and becomes the highest pressure, the motor operates to move the edema measurement unit 1000 upward. For example, the edema measurement unit 1000 presses the skin for 5 seconds, and then moves to the lower portion of the housing in its original position.

If the skin is normal, the skin pressed by the edema measuring unit 1000 will quickly be restored to its original position. However, in the case of skin edema, the skin will not be restored to its original location or it will take a long time to be restored.

The edema measuring unit 1000 measures the time at which the skin is restored after moving to the upper portion through a pressure value equal to the pressure value measured by the pressure measuring sensor 1100.

That is, when the edema measurement unit 1000 presses the skin and returns to the original position, the pressurized skin will gradually restore to the original position over time and will come into contact with the edema measurement unit 1000 returned to the original position. The edema measuring unit 1000 compares the pressure value measured by contacting the skin restored to the original position with the pressure value measured by the pressure measuring sensor 1100. If the pressure value measured by the edema measurement unit 1000 returned to the original position and the pressure value measured by the pressure measurement sensor 1100 are the same, it can be confirmed that the skin is restored to the original position.

The time at which this skin was restored is compared to a preset time. Then, the edema measuring unit 1000 determines that the skin is restored after a preset time and if the skin touches or the skin does not touch after a preset time has elapsed. Thereafter, the edema measurement unit 1000 outputs the result to the display 700.

Through this, the skin condition diagnosis device according to the present invention can determine whether the skin is edema.

In the comprehensive determination unit 850, an output table corresponding to each value of each roughness calculation unit and each step of the sensitivity calculation unit is stored.

The output table may be formed to output a value corresponding to an output value corresponding to the value of the roughness calculator first, and to calculate a predetermined difference according to each step output by the sensitivity calculator.

As an example, the numerical value output by the roughness calculator-(each step of the sensitivity calculator-1) * The calculation can be performed with a predetermined difference.

In one example, if the preset difference is 0.2, the overall determination unit 850 may output the following values.

The roughness calculation unit expressed the roughness of the sample with a numerical value of 7 through a correction equation and outputted it. In addition, assuming that the corresponding EEG is detected in step 5 of the operation of the sensitivity calculation unit, the comprehensive determination unit 850 determines and outputs the skin condition of {7-(5-1)*0.2} as 6.2. If the corresponding EEG is detected in step 1, the comprehensive determination unit 850 outputs 7, and when the corresponding EEG is detected in step 2, it outputs 6.8, and if the corresponding EEG is detected in step 3, it will be 6.6.

Through this, the digitized skin condition can be confirmed.

On the other hand, the operation of the general judgment unit 850 as described above is an example, and it will be understood that the operation is not limited thereto.

Although the present invention has been illustrated and described in relation to specific embodiments, it is understood in the art that the present invention can be variously improved and changed within the limits that do not depart from the technical spirit of the present invention provided by the following claims. It will be obvious for those of ordinary skill.

1: Skin condition diagnosis device
100: standard lighting
200: correction lighting 200a: first correction lighting
200b: Second correction light 200c: Third correction light
200d: 4th correction lighting 200e: 5th correction lighting
200f: 6th calibration lighting 210: 1st calibration lighting group
220: 2nd correction lighting group 230: 3rd correction lighting group
240: 4th correction lighting group 250: 5th correction lighting group
300: CCD camera 400: moisture measurement unit
500: EEG measuring pad 600: Contact pad
700: Display 800: Control
810: current application unit 820: moisture degree calculation unit
830: roughness measurement unit 840: sensitivity measurement unit
850: Comprehensive judgment unit 860: Standard DB
870: brain wave detection unit 880: age computation department
900: housing
910: Reference housing 911: Upper reference unit
912: lower reference part 920: Ministry of Transportation
1000: edema measurement unit 1100: pressure measurement sensor

Claims (8)

A housing including an opening contacting the specimen on one side;
A reference light disposed at a position corresponding to the opening in the interior of the housing to irradiate light at a position perpendicular to the sample, and having an angle set with the reference light to irradiate light at an angle not perpendicular to the sample; and A roughness calculation unit which receives each light reflected when the correction light disposed inside the housing and the reference light and the correction light are irradiated toward the sample, and calculates a roughness of the sample by calculating a difference in luminosity of each light; And
Sensitivity computation unit that measures the EEG and applies current to the sample according to a predetermined step, and calculates the sensitivity of the sample corresponding to the intensity of the current when a corresponding EEG corresponding to the stimulus of the current is detected in the EEG measured.
Skin condition diagnosis device comprising a. According to claim 1,
The housing is formed to include at least one reference point and a symmetrical point disposed at a symmetrical position with an angle set at the reference point,
A CCD camera receiving the reference light and reflected light is disposed at the reference point,
Correction lighting is arranged at the symmetry point
Skin condition diagnosis device characterized in that. According to claim 2,
The symmetry point is formed by forming a plurality of layers along a circumference of the housing.
Skin condition diagnosis device characterized in that. The method of claim 2 or 3,
The roughness calculation unit,
A controller that is connected to the reference lighting, the calibration lighting, and the CCD camera to operate the reference lighting and the calibration lighting according to a predetermined order, and calculates the difference in light intensity of the light received by the CCD camera to calculate the roughness of the specimen.
Skin condition diagnosis device comprising a. According to claim 1,
The sensitivity operation unit,
It is installed adjacent to the opening of the housing, the electroencephalography detection unit for detecting the contact pad and the electroencephalogram which come into contact with the specimen, and the step-by-step current is applied to the contact pad and the contact pad for a set period of time and connected to the electroencephalography detection unit Control unit that detects the corresponding EEG corresponding to the current being applied
Skin condition diagnosis device comprising a. The method of claim 5,
The stepwise current is applied,
It includes an applied area to which an electric current is applied and an unlicensed area to which no current is applied.
Skin condition diagnosis device characterized in that. The method of claim 5,
The current applied in any one of the step-by-step currents is applied to the current of the same intensity multiple times.
Skin condition diagnosis device characterized in that. The method of claim 7,
The control unit,
Correcting the strength of the EEG measured by dividing and summing the EEGs measured during the application of the current of any one step at equal intervals
Skin condition diagnosis device characterized in that.

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