JP7075442B2 - Skin condition detector - Google Patents

Description

The present invention relates to a skin condition detecting device for detecting a skin condition via a protective sheet attached to the skin of a subject.

With the aging of the population, the number of patients requiring long-term treatment is increasing. When these patients are bedridden in the same posture, there is a problem of causing bedsores in the surrounding tissues that have become poorly circulated due to compression at the contact site between the body and the support surface (mostly the bed).
This bed sore starts from the initial redness, and if left untreated, there is a risk that it will worsen in a short period of time to severe diseases such as tissue defects. Therefore, it is necessary to recognize and treat bedsores at the initial redness stage.

However, it is difficult to recognize bedsores in the initial redness stage, and at present, when caregivers and nurses notice the patient's redness, they check whether the bedsores are present by changing the color of the glass plate or finger press. ..
There are individual differences in skin color, and the actual situation is that the initial judgment of redness of the skin is made by experienced doctors, nurses, and the like. However, in many cases, the family is caring for them at home, and it is difficult for an inexperienced person such as a family to make a judgment, and the initial redness may be overlooked and worsened.

In addition, as a countermeasure after finding a pressure sore, a protective sheet is attached to the skin of the found pressure sore to relieve the pressure on the contact area of the skin, and the recovery process of the pressure sore part is observed.
It is desirable to observe this follow-up without peeling off the protective sheet, because if the protective sheet is peeled off and an attempt is made to observe, the peeling of the protective sheet causes pain to the patient and there is a risk of worsening the pressure sore portion.

Therefore, in follow-up observation, the pressure sore part is observed from the top where the protective sheet is attached, but since it is originally a subjective color judgment, the judgment through the protective sheet is not only for inexperienced people such as family members but also for doctors. It will be difficult even for experienced people such as nurses and nurses.
Further, there are a plurality of types of protective sheets prescribed having different light transmission characteristics, and it is difficult to grasp the change in redness of the skin due to the difference in the gloss of the surface and the unevenness of the surface depending on the method of application.

Patent Document 1 is a conventional technique for optically observing pressure sores, and the pressure sore detection device described in Patent Document 1 will be described below.
The floor slip detection device described in Patent Document 1 has a first detection means having one or a plurality of moisture sensors for detecting the amount of water by pressing the detection surface against the skin of the body, and the detection surface is pressed against the skin. A second detection means provided separately from the first detection means, which detects the amount of water by hitting, the amount of water obtained by the first detection means, and the water content obtained by the second detection means. Based on the difference from the amount, the determination means for determining the risk of floor slippage indicating the possibility that the portion to which the detection surface of the moisture sensor of the first detection means is pressed is the floor slippage, and the determination result of the determination means. It is equipped with a display device for displaying. Then, the pressure sore is determined based on the difference between the water content of the pressure sore portion obtained by the first detection means and the water content of the comparative skin obtained by the second detection means.

Further, although it is not an observation of floor slippage, in Patent Document 2, as a contact allergy test sheet, an test sheet in which an allergen is placed on a transparent sheet is adhered to the skin, and an optical sheet is optically applied from above the transparent sheet. A technique for directly detecting a change in skin color by a method is described.

Japanese Patent No. 5922457 (Page 1, FIG. 1) Japanese Unexamined Patent Publication No. 2001-55346 (page 1)

The conventional example shown in Patent Document 1 is a bed sore detection device common to the present invention, but detects the water content by directly pressing the detection surface against the pressure sore portion of the skin. Therefore, if the protective sheet is attached to the pressure sore on the skin, the protective sheet must be peeled off for measurement, which causes the patient to suffer from peeling off the protective sheet.
Further, the prior art shown in Patent Document 2 does not relate to a bed sore detecting device, and a method of optically detecting a skin color regardless of the presence or absence of a translucent sheet adhered to the skin is specific. Not listed in.

An object of the present invention is to observe the condition of the affected area directly from the protective sheet on the skin of the affected area such as a bed sore, and to correct the optical characteristics of the protective sheet to enable accurate follow-up observation. It is to provide a detection device.

In order to achieve the above object, the configuration of the skin condition detection device in the present invention is a skin condition detection device for detecting the condition of the skin, and the reflection of each of the red, green, and blue wavelength bands reflected by the skin. A detection unit for detecting light intensity, red reflected light which is the reflected light of the red wavelength band, green reflected light which is the reflected light of the green wavelength band, or blue which is the reflected light of the blue wavelength band. It has a control unit that determines the state of the skin based on the light intensity of any of the reflected light, and the control unit has the red reflected light and the said red reflected light for each assumed state of the skin. The reflected light to be used is selected from the green reflected light or the blue reflected light, and the skin condition to be determined is due to the floor displacement, and when the initial symptom of the floor displacement is detected, the red reflected light is used. It is characterized in that only the red reflected light and the blue reflected light are used when determining the skin condition in which the symptom of floor slippage has progressed .

As described above, the skin condition detecting device of the present invention is a skin condition detecting device for observing the progress of the affected part by comparing the reflected light from the affected part with the skin and the protective sheet, and the affected part with the protective sheet is attached. Accurate skin condition detection can be performed by adding correction based on the optical characteristics of the protective sheet to the reflected light in each of the red, green, and blue wavelength bands.

It is a perspective view which shows the skin condition detection apparatus in 1st Embodiment of this invention. FIG. 3 is a partial cross-sectional view showing a cross section taken along the line AA in the skin condition detecting device shown in FIG. 1. FIG. 3 is a partial cross-sectional view showing a cross section taken along the line AA in a modified example of the skin condition detecting device shown in FIG. 1. It is a block diagram which shows the circuit structure of the skin condition detection apparatus in 1st Embodiment of this invention. It is a schematic diagram which shows the use example of the skin condition detection apparatus in 1st Embodiment of this invention. It is a schematic diagram which shows the use example of the skin condition detection apparatus in 1st Embodiment of this invention. It is a schematic diagram explaining the optical operation of the light source and the detection part in 1st Embodiment of this invention. It is a schematic diagram explaining the optical operation of the light source and the detection part in 1st Embodiment of this invention. It is a flowchart explaining the operation of the skin condition detection apparatus in 1st Embodiment of this invention. It is a table explaining the operation of the skin condition detection apparatus in 1st Embodiment of this invention. It is a table explaining the operation of the skin condition detection apparatus in 1st Embodiment of this invention. It is a graph explaining the operation of the skin condition detection apparatus in 1st Embodiment of this invention. It is a graph explaining the operation of the skin condition detection apparatus in 1st Embodiment of this invention. It is a graph explaining the operation of the skin condition detection apparatus in 1st Embodiment of this invention. It is a graph explaining the operation of the skin condition detection apparatus in 1st Embodiment of this invention. It is a perspective view which shows the skin condition detection apparatus in the 2nd Embodiment of this invention.

Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. However, the embodiments shown below exemplify a skin condition detecting device for embodying the idea of the present invention, and the present invention is not limited to the following configurations. In particular, the dimensions, materials, shapes, relative arrangements, etc. of the components described in the embodiments are not intended to limit the scope of the present invention to that alone unless otherwise specified, and are merely explanatory examples. Not too much. In the following description, the same parts and components may be given the same name and reference numeral, and detailed description thereof may be omitted as appropriate.
Further, in the description of the following embodiments, a skin condition detecting device for observing the skin condition of bedsores will be described as an example.

[First Embodiment]
The skin condition detection device of the first embodiment of the present invention will be described with reference to FIGS. 1 to 8.
FIG. 1 is a perspective view showing the configuration of the skin condition detecting device of the first embodiment. 2A is a partial cross-sectional view showing an AA cross section in the skin condition detecting device shown in FIG. 1, FIG. 2B is a partial cross-sectional view showing an AA cross section in a modified example of the skin condition detecting device shown in FIG. 1, FIG. Is a block diagram showing a circuit configuration of the skin condition detection device shown in FIG. 1.

[Explanation of Configuration of First Embodiment]
The skin condition detection device 1 shown in FIG. 1 is provided with a measurement unit 3 on the front surface of a rectangular case 2, and the configuration of the measurement unit 3 includes a light source 4 for irradiation and a detection unit 5, and the periphery thereof is black. A contact member 6 made of an elastic body is provided.
Further, on the upper surface of the case 2, a switch 7 for controlling the measurement operation of the skin condition detection device 1 and a display unit 8 for displaying the measurement result of the skin condition detection device 1 are provided.
As will be described later, a battery for a power source, a measurement circuit, and the like are built in the case 2 of the skin condition detection device 1.

FIG. 2A is a partial cross-sectional view showing the AA cross section of the skin condition detection device 1 shown in FIG. 1, wherein the detection unit 5 is a red light sensor 5r (hereinafter referred to as “R sensor 5r”) for detecting red light. It has a green light sensor 5g (hereinafter referred to as "G sensor 5g") and a blue light sensor 5b (hereinafter referred to as "B sensor 5b"), and from the white light emitted from the light source 4, the red component R, respectively. The green component G and the blue component B are detected. The periphery of the R sensor 5r, the G sensor 5g, and the B sensor 5b constituting the light source 4 and the detection unit 5 is covered with a black contact member 6, and the optical detection operation of the light source 4 and the detection unit 5 is performed. Prevents the entry of external light.
Further, the flexibility of the frame-shaped portion 6a provided at the tip of the contact member 6 allows the measuring portion 3 to come into close contact with the skin of the human body.

In the skin condition detection device 1, the intensity of the reflected light reflected by the white light emitted from the light source 4 by the skin or the protective sheet is measured by the R sensor 5r, the G sensor 5g, and the B sensor 5b constituting the detection unit 5. , Red component R, green component G, and blue component B are detected. At this time, the white component W, which is the sum of the reflected light intensities of the red component R, the green component G, and the blue component B, may be detected as the reflected light intensity.
When detecting as the reflected light intensity of the white component W, a white light sensor 5w (hereinafter referred to as "W sensor 5w") is further provided in the detection unit 5 as a white light detection unit as shown in FIG. 2B as a modification. The white component W may be directly detected by the W sensor 5w.
According to the configuration of FIG. 2B, the number of sensors is increased by one, but it is directly detected by the W sensor 5w from the white component W obtained by adding up the three-color light detected by the R sensor 5r, the G sensor 5g, and the B sensor 5b shown in FIG. 2A. The detection accuracy of the reflected light intensity of the white component W is high, which is advantageous for the operation of detecting the skin condition.

[Explanation of circuit configuration of skin condition detection device]
Next, the circuit configuration of the skin condition detection device 1 will be described with reference to FIG.
FIG. 3 is a block diagram showing a circuit configuration of the skin condition detection device 1, which is composed of a control unit 10 built in the case 2 in addition to the measurement unit 3, the measurement switch 7, and the display unit 8.
The control unit 10 has a switch count determination unit 11 that determines the number of operations of the measurement switch 7, a control circuit 12 that receives signals from the switch count determination unit 11 and outputs various control signals, and a control signal from the control circuit 12. In response to this, the detection light from the R sensor 5r, G sensor 5g, and B sensor 5b constituting the detection unit 5 of the measurement unit 3 is input, and the red component R (hereinafter referred to as "R value") which is an optical signal is described. ), Green component G (hereinafter referred to as "G value"), Blue component B (hereinafter referred to as "B value") are detected, and a white component obtained by synthesizing R value, G value and B value. It has an optical signal processing unit 13 that calculates W (hereinafter referred to as “W value”), and a determination circuit unit 14 that performs various determination operations based on each optical signal from the optical signal processing unit 13.

Further, the determination circuit unit 14 has a total optical signal Pha (R value, G value, B value) calculated from the detected optical signal Phc (R value, G value, B value) from the optical signal processing unit 13 and the detected optical signal Phc. There is a protective sheet from the storage unit 15 that stores the total W value), the protective sheet determination unit 16 that receives the total optical signal Pha from the storage unit 15 and determines the presence or absence of the protective sheet, and the protective sheet determination unit 16. The signal Sa, the correction coefficient calculation unit 17 that calculates the correction coefficient α by receiving the optical characteristic value by the protective sheet, and the detection optical signal Phc1 (R1 value, G1 value, B1 value) supplied from the storage unit 15 are corrected. The correction unit 18 for creating the detection optical signal Phc2 (R2 value, G2 value, B2 value) corrected by the correction coefficient α supplied from the coefficient calculation unit 17 and the detection optical signal Phc2 supplied from the correction unit 18 are preset. It has a skin condition determination unit 19 for determining whether or not the floor is displaced by comparing with the reference value.

In the above, an example in which the detection unit 5 is composed of the R sensor 5r, the G sensor 5g, and the B sensor 5b has been described. However, the W sensor 5w is further provided as the white light detection unit, and the white component W is directly provided by the W sensor 5w. Detection may be performed. In that case, it is not necessary for the optical signal processing unit 13 to add up the R value, the G value, and the B value to calculate the W value.

FIG. 3 shows a configuration example in which information on the reflected light intensity detected by the detection unit 5 is stored in the storage unit 15 via the optical signal processing unit 13, but the optical signal processing unit 13 does not provide the storage unit 15. It is also possible to supply the detected optical signal Phc and the total optical signal Pha directly to the protective sheet determination unit 16, the correction unit 18, and the floor displacement determination unit 19.

[Explanation of the operation method and operating principle of the skin condition detection device]
Next, the operation method and the operation principle of the skin condition detection device 1 will be described with reference to FIGS. 4A to 5B. 4A and 4B are schematic views showing a state in which the measurement unit 3 of the skin condition detection device 1 is pressed against the skin of the subject to perform the detection operation, and FIG. 4A is a schematic diagram showing the non-compression portion 103 of the skin without the protective sheet 200. The reference skin color measurement state in which the measurement unit 3 of the skin condition detection device 1 is pressed is shown, and FIG. 4B shows the measurement unit 3 of the skin condition detection device 1 pressed against the skin compression part 102 to which the protective sheet 200 is attached. The target skin color measurement state is shown. 5A and 5B are schematic views showing the light detection operation of the light source 4 and the detection unit 5 in the reference skin color measurement state and the target skin color measurement state shown in FIGS. 4A and 4B.

In FIGS. 4A to 5B, a protective sheet 200 is adhered to the reddish portion 101 due to the pressure sore of the skin 100 to protect the reddish portion 101. The portion of the skin 100 to which the protective sheet 200 is adhered is the compression portion 102, and the portion where the protective sheet 200 is not adhered is the non-compression portion 103.
4A shows a reference skin color measurement state in which the measurement unit 3 of the skin condition detection device 1 is pressed against the non-compression portion 103 to which the protective sheet 200 is not adhered, and FIG. 4B shows the measurement of the skin condition detection device 1. The target skin color measurement state in which the portion 3 is pressed against the compression portion 102 to which the protective sheet 200 is adhered is shown.
When the measuring unit 3 of the skin condition detecting device 1 is pressed against the skin 100 or the protective sheet 200, the measuring unit 3 protects the skin 100 or the skin 100 by the flexibility of the frame-shaped portion 6a provided at the tip of the contact member 6. It is in close contact with the sheet 200.

5A and 5B are schematic views showing the optical operation of the light source 4 and the detection unit 5 in a state where the measurement unit 3 of the skin condition detection device 1 is pressed against the skin of the subject to perform the detection operation. 5A corresponds to the reference skin color measurement state shown in FIG. 4A, and FIG. 5B corresponds to the target skin color measurement state shown in FIG. 4B.

That is, in the reference skin color measurement state of FIG. 5A, all the light rays P1 emitted from the light source 4 are reflected by the non-compression portion 103 of the skin 100 and received by the detection unit 5 as the reflected light P2.
In the target skin color measurement state of FIG. 5B, most of the light rays P1 emitted from the light source 4 are reflected by the surface of the protective sheet 200 and received by the detection unit 5 as reflected light P3 (indicated by a dotted line). Further, a part of the light beam P1 passes through the protective sheet 200, is reflected by the compression portion 102 of the skin 100, and is received by the detection unit 5 as the reflected light P4.

As will be described later, in the target skin color measurement state shown in FIG. 5B, depending on the type and attachment method of the protective sheet 200, a component that mirror-reflects on the surface of the protective sheet 200 is included, so that the reflected light P3 and the reflected light P4 are combined. The reflected light has higher brightness of each of the R value, the G value, and the B value than the reflected light P2 in the reference skin color measurement state shown in FIG. 5A.

Next, an operation example of the skin condition detection device 1 will be described with reference to the schematic views shown in FIGS. 4A to 5B according to the circuit configuration diagram shown in FIG.
First, when the skin condition detection device 1 is set to the reference skin color measurement state shown in FIG. 4A and the measurement switch 7 is operated once, the first operation signal is output from the switch count determination unit 11 and this first operation is performed. The control circuit 12 is set to the reference skin color measurement mode by the signal, and the measurement unit 3 and the optical signal processing unit 13 are controlled to the reference skin color measurement state.
As a result, the light source 4 constituting the measuring unit 3 repeats the light emitting operation 10 times, and the R sensor 5r, the G sensor 5g, and the B sensor 5b constituting the detecting unit 5 each have 10 Rt values as reference value signals. The Gt value and the Bt value are received and supplied to the optical signal processing unit 13.

When the optical signal processing unit 13 is supplied with 10 Rt values, Gt values, and Bt values, the Rt value, Gt value, and Bt value obtained by averaging the 10 data are calculated. Further, the Wt value obtained by adding the averaged Rt value, Gt value, and Bt value is calculated, and the calculated Wt value is used as the reference value of the total optical signal Pha0 and the averaged Rt value, Gt value, and Bt value. The detection optical signal Phc0 of the reference value is stored in the storage unit 15.

Next, when the skin condition detection device 1 is set to the target skin color measurement state shown in FIG. 4B and the measurement switch 7 is operated once, the second operation signal is output from the switch count determination unit 11, and this second operation signal is output. The control circuit 12 is set to the target skin color measurement mode by the operation signal, and the measurement unit 3 and the optical signal processing unit 13 are controlled to the target skin color measurement state.
As a result, the light source 4 constituting the measuring unit 3 repeats the light emitting operation 10 times, and the R sensor 5r, the G sensor 5g, and the B sensor 5b constituting the detecting unit 5 each have 10 R values as measurement value signals. The G value and the B value are received and supplied to the optical signal processing unit 13.

When 10 R-values, G-values, and B-values are supplied, the optical signal processing unit 13 calculates R-values, G-values, and B-values obtained by averaging 10 pieces of data, respectively. Further, the W value obtained by adding the averaged R value, G value, and B value is calculated, and the calculated W value is used as the total optical signal Pha1 of the measured value and supplied to the storage unit 15, and the averaged R value, The G value and B value are stored in the storage unit 15 as the detected optical signal Phc1 (R1 value, G1 value, B1 value) of the measured value.

When all the data of the total optical signal Pha0 of the stored reference value and the total optical signal Pha1 of the measured value are prepared, the storage unit 15 supplies the stored data to the protection sheet determination unit 16. The protective sheet determination unit 16 calculates Pha1-Pha0 = ΔW from the supplied data.
This ΔW is the difference in the amount of reflected light from the non-compressed portion 103 of the skin 100 and the protective sheet 200, and if the difference in the amount of reflected light ΔW is larger than the predetermined comparison value M, it is determined that the protective sheet is present at the measurement location. If the reflected light amount difference ΔW is smaller than the predetermined comparison value M, it is determined that there is no protective sheet at the measurement location. Then, in the case of determination with the protective sheet, the reflected light amount difference ΔW is supplied to the correction coefficient calculation unit 17 together with the signal Sa with the protective sheet, and in the case of determination without the protective sheet, the signal Sn without the protective sheet is supplied to the correction unit 18. do.

The correction coefficient calculation unit 17 supplied with the signal Sa with the protective sheet and the reflected light amount difference ΔW calculates the correction coefficient α. The correction coefficient α is a value obtained by dividing the reflected light amount difference ΔW into three equal parts of R, G, and B, is calculated by α = ΔW / 3, and supplies this correction coefficient α to the correction unit 18.
The correction unit 18 supplied with the correction coefficient α adds the correction coefficient α to each of the R1 value, G1 value, and B1 value of the detection optical signal Phc1 (R1 value, G1 value, B1 value) supplied from the storage unit 15. The corrected detection optical signal Phc2 (R2 value, G2 value, B2 value) is supplied to the floor displacement determination unit 19.
Further, when the determination of the protective sheet determination unit 16 is the determination of no protective sheet and the signal Sn without the protective sheet is supplied to the correction unit 18, the correction unit 18 does not perform the correction operation and stores the detection light. The data of the signal Phc1 is supplied to the floor displacement determination unit 19 as the detected optical signal Phc2 (R2 value, G2 value, B2 value) as it is.

The bed sore determination unit 19 to which the detection optical signal Phc2 (R2 value, G2 value, B2 value) is supplied from the correction unit 18 compares each R2 value, G2 value, and B2 value with the preset reference value X, and R2. If any one of the value, the G2 value, and the B2 value is larger than the reference value X, it is determined that the pressure sore is large, and the pressure sore display and the color of the pressure sore portion are displayed on the display unit 8.

When detecting only the redness of the initial symptom of bedsore, the redness becomes stronger, so it is possible to judge the bed sore using only the R2 value, or when the skin condition that the symptom of the bed sore progresses and becomes reddish black is judged. Can also determine the skin condition using the R2 value and the B2 value. It is also possible to set the reference value X for each of the R2 value, the G2 value, and the B2 value, and determine a plurality of symptoms in detail by combining the results of comparison with the reference value X for each color component.

When a W sensor 5w, which is a white light detection unit, is provided in the detection unit 5, and the white component W is directly detected by the W sensor 5w, the optical signal processing unit 13 sets the total optical signal Pha0 and the total optical signal Pha1. , 10 Wt values or 10 Wt values detected by the W sensor 5w, instead of calculating the Wt value or W from the averaged Rt value, Gt value, Bt value or averaged R value, G value, B value. The W value is averaged, and the averaged Wt value and W value are supplied to the storage unit 15 as Pha0 and Pha1, and the protective sheet determination unit 16 calculates ΔW by the Pha0 and Pha1 to determine the presence or absence of the protective sheet. conduct.

In the method of directly detecting the white light by providing the W sensor 5w for detecting the white light in the measuring unit 3, the R value, the G value, and the B value are measured by the R sensor 5r, the G sensor 5g, and the B sensor 5b shown in FIG. 2A. It is superior in characteristics to the method of individually measuring and adding. The reason is that the characteristic values of the R sensor 5r, G sensor 5g, and B sensor 5b vary, and the detected R value, G value, and B value deviate slightly from the true value. However, the value is slightly different from the W value directly measured by the W sensor 5w.

As described above, in the configuration of the modified example of the skin condition detecting device 1 shown in FIG. 2B, the W sensor 5w is increased by one, but the accuracy of the detected white light is increased, and the overall measurement accuracy is increased. Has the effect of increasing.

[Explanation of the flowchart showing the operation of the skin condition detection device]
Next, the flow of operation of the skin condition detection device 1 will be described with reference to the flowchart shown in FIG. Also in this flowchart, the circuit configuration diagram shown in FIG. 3 and the schematic diagrams shown in FIGS. 4A and 4B are referred to.
Step S1 is a measurement start mode in which the skin condition detection device 1 is turned on. Step S2 is a reference skin color measurement mode, in which the skin condition detection device 1 shown in FIG. 4A is applied to the non-compression portion 103 of the skin 100, and the measurement switch 7 is operated. Step S3 is a reference skin color value detection mode, in which 10 Rt values, Gt values, and Bt values supplied by the optical signal processing unit 13 from each of the R sensor 5r, the G sensor 5g, and the B sensor 5b are averaged. The Rt value, Gt value, and Bt value obtained by averaging 10 pieces of data are calculated. Further, the Wt value obtained by adding the averaged Rt value, Gt value, and Bt value is calculated, and the calculated Wt value is used as the reference value of the total optical signal Pha0 and the averaged Rt value, Gt value, and Bt value. The detection optical signal Phc0 of the reference value is supplied to the storage unit 15 and stored.

Step S4 is a target skin color measurement mode, in which the skin condition detection device 1 shown in FIG. 4B is applied to the compression portion 103 on which the protective sheet 200 is attached to the skin 100, and the measurement switch 7 is operated. Step S5 is a target skin color value detection mode, in which 10 R values, G values, and B supplied by the optical signal processing unit 13 from each of the R sensor 5r, the G sensor 5g, and the B sensor 5b are averaged to 10 each. The R value, G value, and B value obtained by averaging the pieces of data are calculated. Further, the W value obtained by adding the averaged R value, G value, and B value is calculated, and the calculated W value is used as the total optical signal Pha1 of the measured value and the averaged R value, G value, and B value. The detected optical signal Phc1 of the measured value is supplied to the storage unit 15 and stored.

Step 6 is a mode for determining the presence / absence of a protective sheet, and the sheet determination unit 16 calculates the light amount difference ΔW from the reference value Pha0 (W0) and the measured value Pha1 (W1) stored in the storage unit 15 to calculate the protective sheet. Judge the presence or absence of. As an example, assuming that the amount of light reflected from the protective sheet 200 is 5 times or more the amount of light reflected from the non-compressed portion 103 of the skin as a reference, the specific value H is set to 5. Then, the presence or absence of the protective sheet is determined by "W1-W0 = ΔW>5". When ΔW> 5, it is assumed that there is a protective sheet, and the correction coefficient calculation unit 17 is supplied with the light amount difference ΔW together with the signal Sa with the protective sheet.

Step S7 is a correction value calculation mode, and the correction value calculation unit 17 starts operation by the protection sheet presence signal Sa supplied from the protection sheet determination unit 16 to change the light amount difference ΔW into three colors of R, G, and B. The correction value α for each correction is calculated. That is, the calculation formula of the correction value α is the following α = ΔW / 3.

Step S8 is a correction processing mode, and the correction unit 18 corrects the detection light signal Phc1 (R1 value, G1 value, B1 value) of the measured value supplied from the storage unit 15 by adding the correction value α. Create Phc2 (R2 value, G2 value, B2 value). That is, the calculation formula for the correction process is as follows. {R2 = R1-α, G2 = G1-α, B2 = B1-α}.

Step S9 is a mode without correction processing, and in the determination of step S6, in the case of determination without a protective sheet, the correction unit 18 supplied with the protection sheet-less signal Sn is the detection optical signal of the measured value supplied from the storage unit 15. The Phc1 (R1 value, G1 value, B1 value) is converted into a corrected detection optical signal Phc2 (R2 value, G2 value, B2 value) without any correction.

The correction unit 18 supplies the corrected detection optical signal Phc2 (R2 value, G2 value, B2 value) to the bed sore determination unit 19 regardless of whether the signal Sa with the protective sheet or the signal Sn without the protective sheet is received. Of these corrected detection optical signal Phc2 data, the data based on the signal Sa with the protective sheet is the data measured through the protective sheet which is the object of the present invention, and the data based on the signal Sn without the protective sheet is the floor displacement. This is the measured data when the affected area is not covered with a protective sheet.
That is, the skin condition detection device 1 in the present invention can be used both when the protective sheet is used and when the protective sheet is not used.

Step S10 is a skin color difference calculation mode, and the floor displacement determination unit 19 has a reference value detection light signal Phc0 supplied from the storage unit 15 and a corrected detection light signal Phc2 (R2 value, G2 value) supplied from the correction unit 18. , B2 value), and the skin color difference ΔR, ΔG, ΔB for each of R, G, and B is calculated. The calculation formula is ΔR = R2-R0, ΔG = G2-G0, and ΔB = B2-B0.

Step S11 is a bed sore determination mode, in which the bed sore determination unit 19 compares the calculated skin color differences ΔR, ΔG, and ΔB with a predetermined reference value X, and even one of the skin color differences ΔR, ΔG, and ΔB is from the specific value X. If it is large, it is judged that the bed sore. Then, the display unit 8 displays whether or not there is a pressure sore and displays a skin color larger than the specific value X. Further, if all of the skin color differences ΔR, ΔG, and ΔB are smaller than the specific value X, the display unit 8 is displayed to indicate that there is no pressure sore.

Next, using FIGS. 7A and 7B, the operation based on the flowchart of FIG. 6 will be described as a determination example using actual measured values.
FIG. 7A is a table showing an example of measured values in each step when the skin of the subject's bedsore is protected by a protective sheet.
In FIG. 7A, step S3 is the reference skin color value detection mode in FIG. 6, which is a measured value of the non-compressed portion 103 of the skin 100, R0 = 21, G0 = 16, B0 = 11, and the R0, G0. W0 = 51 calculated from B0. The numerical value of each color becomes the reference value for pressure sore determination.

Step S5 is the target skin color value detection mode in FIG. 6, which is a measured value of the compression portion 102 in which the protective sheet 200 is adhered to the pressure sore portion of the skin 100, and is R1 = 30, G1 = 20, B1 = 13. Yes, W1 = 62 calculated from these R1, G1, and B1.
The measured value in step 5 is higher than that in step 3 because the reflected light is increased by the surface reflection of the protective sheet 200.
Step S6 is a mode for determining the presence / absence of a protective sheet, and the light amount difference of white light ΔW = W1-W0 = 62-51 = 11. Since the predetermined specific value H is set to 5, it is determined that there is a protective sheet because the light amount difference ΔW (11) is larger than the specific value H (5).

Step S7 is a correction coefficient calculation mode, in which the correction coefficient calculation unit 17 is supplied with the protection sheet presence signal Sa and the light amount difference ΔW (11) from the protection sheet determination unit 16 to calculate the correction coefficient α. The formula for calculating α is α = ΔW / 3 = 11/3 = 3.667.
Step S8 is a correction processing step, and the correction unit 18 corrects the detection optical signal Phc1 (R1, G1, B1) supplied and stored by the optical signal processing unit 13 from the correction coefficient calculation unit 17. The detection optical signal Phc2 (R2, G2, B2) is created by adding and correcting the coefficient α = 3.667. The calculation formula of the detected optical signal Phc2 (R2, G2, B2) is R2 = R1-α = 30-3.667 = 26.3, G2 = G1-α = 20-3.667 = 16.3, B2. = B1-α = 13-3.667 = 9.3.

Step S10 is a skin color difference calculation mode, in which the floor displacement determination unit 19 has a reference value detection optical signal Phc0 (R0, G0, B0) supplied from the storage unit 15 and a detection optical signal Phc2 (R0, G0, B0) supplied from the correction unit 18. The chromaticity difference of each color is obtained from the difference from R2, G2, B2). The formula for calculating the skin color difference is ΔR = R2-R0 = 26.3-21 = 5.3, ΔG = G2-G0 = 16.3-16 = 0.3, ΔB = B2-B0 = 9.3-. 11 = -1.7.

Step S11 is a pressure sore determination step, and the pressure sore determination unit 19 compares the chromaticity difference ΔR, ΔG, ΔB of each color of the detected detection optical signal Phc2 (R2, G2, B2) with a predetermined specific value. Judge whether or not. Since the specific value X is set to 5, when the chromaticity differences ΔR = 5.3, ΔG = 0.3, and ΔB = -1.7 of each color are compared with X = 5, respectively, ΔR (5.3) ≧. Since it is X (5), it is determined that there is a pressure sore, and the result is displayed on the display unit 8 to end the skin condition detection measurement.

Next, FIG. 7B is a table showing an example of the measured values in each step when the skin of the subject's bedsore is not protected by the protective sheet. 7A and 7B compare the case where the protective sheet 200 is attached to the skin 100 of the subject having the same pressure sore state and the case where the protective sheet 200 is not attached. Further, in FIG. 7B, the same steps as those in FIG. 7A have basically the same contents, duplicate explanations are omitted, and only the differences are described.

In FIG. 7B, step S3 is the same reference skin color value detection mode as step S3 in FIG. 7A. The measured values of the non-compressed portion 103 of the skin 100 are the same as R0 = 21, G0 = 16, B0 = 11, and W0 = 51 calculated from these R0, G0, B0 is also the same.

Step S5 is the target skin color value detection mode in FIG. 6, which is a measured value of the non-compression portion 103 in which the protective sheet 200 is not adhered to the pressure sore portion of the skin 100, and is R1 = 26, G1 = 16, B1. = 10, which is different from FIG. 7A. W1 = 52 calculated from R1, G1 and B1 is also different from FIG. 7A.

Step S6 is a mode for determining the presence / absence of a protective sheet, and the light amount difference ΔW = W1-W0 = 52-51 = 1. Since the predetermined specific value H is set to 5, it is determined that there is no protective sheet because the light amount difference ΔW (1) is smaller than the specific value H (5).

Although step S7 is the correction value calculation mode, the correction coefficient α is not calculated because the protection sheet determination unit 16 does not supply the protection sheet presence signal Sa. Then, the correction unit 18 is supplied with the protection sheet-less signal Sn from the protection sheet determination unit 16, so that the detection light signal Phc1 (R1, G1, B1) supplied from the storage unit 15 is not corrected and the detection light is detected as it is. It is supplied to the floor displacement determination unit 19 as a signal Phc2 (R2, G2, B2).

Step S10 is a skin color difference calculation mode, and the floor displacement determination unit 19 has a reference value detection optical signal Phc0 (R0, G0, B0) supplied from the storage unit 15 and a detection optical signal Phc2 supplied from the correction unit 18. The chromaticity difference of each color is obtained from the difference from (R2, G2, B2). The formula for calculating the skin color difference is the same as in the case described with reference to FIG. 7A, ΔR = R2-R0 = 26-21 = 5, ΔG = G2-G0 = 16-16 = 0, ΔB = B2-B0 = 10-. 11 = -1.

Step S11 is a pressure sore determination step, and the pressure sore determination unit 19 compares the chromaticity difference ΔR, ΔG, ΔB of each color of the detected detection optical signal Phc2 (R2, G2, B2) with a predetermined specific value. Judge whether or not. Since the specific value X is set to 5, the chromaticity difference ΔR = 5, ΔG = 0, and ΔB = -1 of each color are compared with X = 5, respectively, and ΔR (5) ≧ X (5), which is a pressure sore. Is determined. Then, the result is displayed on the display unit 8 to end the skin condition detection measurement.

Next, a case where the protective sheet 200 is attached to the skin 100 of the subject having the same pressure sore state shown in FIGS. 7A and 7B and a case where the protective sheet 200 is not attached will be compared. ..
In the target skin color measurement mode in step S5, in the case with the protective sheet shown in FIG. 7A and in the case without the protective sheet shown in FIG. 7B, for example, the total optical signal corresponds to W1 = 62 in the case with the protective sheet. When there is no protective sheet, it is significantly different from W1 = 52. However, the result of the skin color calculation in step S10 is that each color difference ΔR = shown in FIG. 7B is compared with each color difference ΔR = 5.3, ΔG = 0.3, ΔB = 1.7 shown in FIG. 7A after correction. 5, ΔG = 0, ΔB = 1, which are very close values. This indicates that sufficiently accurate data can be obtained even if the progress measurement is performed with the protective sheet 200 attached to the pressure sore on the skin 100 of the subject.

Next, using FIGS. 8A to 8D, the relationship between the measured value and the corrected value when the skin of the subject without bedsore is protected by a protective sheet will be described. 8A and 8B and FIGS. 8C and 8D show measurement graphs for two subjects. 8A and 8C show actual measurement values (without correction), and FIGS. 8B and 8D show the state when correction is performed. The horizontal axis shows the measurement time, and the vertical axis shows the amount of light (reflected light intensity) reflected by the skin 100 or the protective sheet 200 from the light source 4. The left half of the graph shows the amount of reflected light of the non-compressed portion 103 of the skin 100, the right half shows the amount of reflected light of the protective sheet, W shows the amount of white light, and R, G, and B each show the amount of reflected light of color light. ing

The amount of light referred to here is originally expressed in units of [μW / cm2], but in the graphs shown in FIGS. 8A to 8D, the measured value of the amount of light [μW / cm2] is A / D converted to 0. The numerical value [counts] expressed by the dynamic range of 256 is shown.

8A and 8B show the measurement results of the subject A, and in the measured value graph shown in FIG. 8A, the white light amount Wa in the portion without the protective sheet in the first half of the left side is 69.06, while the protection in the latter half of the right side. The amount of white light Wb in the sheet 200 portion is as large as 74.67. Further, R, G, and B are also increased due to the influence of the white light amount Wb.
However, in the corrected graph shown in FIG. 8B, the light amounts of R, G, and B in the portion without the protective sheet 200 and the portion with the protective sheet 200 are almost the same level after the influence of the protective sheet 200 is corrected. It is the amount of light.

8C and 8D show the measurement results of subject B, and in the measured value graph shown in FIG. 8C, the white light amount Wa in the portion without the protective sheet 200 in the first half of the left side is 67.38, whereas the amount Wa in the latter half of the right side is 67.38. The amount of white light Wb in the portion of the protective sheet 200 is as large as 76.97. Further, R, G, and B are also greatly affected by the amount of white light Wb.
However, in the corrected graph shown in FIG. 8D, the light amounts of R, G, and B in the portion without the protective sheet 200 and the portion with the protective sheet 200 are almost the same level after the influence of the protective sheet 200 is corrected. It is the amount of light.

As described above, the skin condition detection device of the present invention has the effect of correcting the influence of the protective sheet 200 even for two subjects having different white light amounts Wa in the portion without the reference protective sheet. It is possible to confirm the correct healing progress even if the follow-up of the pressure sore portion is performed with the protective sheet 200 attached without change.

In the description of the first embodiment, the white light from the light source 4 is applied to the skin 100 or the protective sheet 200, and the reflected light intensities of the reflected red, green, and blue wavelength bands are added up to reflect the white component W. An example of detecting the light intensity and an example of further providing a white light sensor 5w and directly detecting the reflected light intensity of the white component W by the white light sensor 5w have been described. However, the skin 100 detected by the detection unit 5 has been described. Difference between the reflected light intensity of the red component R, the green component G, and the blue component B reflected from the protective sheet 200 and the reflected light intensity of the red component R, the green component G, and the blue component B reflected from the protective sheet 200. It is also possible to correct the reflected light intensity of the red component R, the green component G, and the blue component B based on the above, and to grasp the accurate color of the skin 100.

[Second Embodiment]
Next, the skin condition detection device 30 according to the second embodiment of the present invention will be described with reference to FIG.
FIG. 9 shows the configuration of the skin condition detection device 30 in the second embodiment, and the basic configuration of the skin condition detection device 30 is the same as that of the skin condition detection device 1 shown in FIG. 1, and the same element or the corresponding element has the same number. Is added, and duplicate explanations are omitted.

The difference between the skin condition detection device 30 and the skin condition detection device 1 is that the skin condition detection device 1 is integrally configured as a whole, whereas the skin condition detection device 30 is a part of the case 2 in the skin condition detection device 1. Is a two-body configuration consisting of a probe 32 for measurement and a main body 31 connected to the probe 32 with a cord 33. The circuit portion provided inside the skin condition detecting device 1 is provided inside the main body 31, and the display unit 8 is provided on the surface of the main body 31 with a larger screen size.

To operate the skin condition detection device 30, the power supply is operated on the main body 31 side to put the skin condition detection device 30 into an operating state, the measuring unit 3 of the probe 32 is in contact with the skin 100 of the subject, and the switch 7 is operated. The measurement can be performed and the measurement result can be confirmed on the display unit 8 having a large screen size of the main body 31.

In FIG. 9, an example in which the skin condition detection device 30 is connected to the probe 32 for measurement and the main body 31 by a cord 33 has been described, but the configuration is such that the skin condition detection device 30 is wirelessly connected by a general-purpose wireless communication means instead of the cord 33. You can also.

As described above, in the present invention, the skin condition detecting device enables accurate progress (recovery state) observation by an optical device while the affected part of the skin is protected by a protective sheet, and causes pain due to peeling of the protective sheet to the subject. The treatment can be continued.
Further, although the pressure sore has been described as an application example of the skin condition detecting device of the present invention, it is not limited to this, and it is natural that it can be applied to a general injury-related disease, a burn-related disease, and the like.

1, 30 Skin condition detection device 2 Case 3 Measurement unit 4 Light source 5 Detection unit 5r R sensor 5g G sensor 5b B sensor 5w W sensor 6 Contact member 6a Frame shape unit 7 Switch 8 Display unit 10 Control unit 11 Switch count determination unit 12 Control circuit 13 Optical signal processing unit 14 Judgment circuit unit 15 Storage unit 16 Protective sheet Judgment unit 17 Correction coefficient calculation unit 18 Correction unit 19 Floor displacement judgment unit 31 Main unit 32 Probe 33 Code 100 Skin 101 Redness 102 Compression unit 103 Non-compression unit 200 Protective sheet

Claims (1)

It is a skin condition detection device for detecting the condition of the skin.
A detection unit for detecting the intensity of reflected light in each of the red, green, and blue wavelength bands reflected by the skin, and
Of the reflected light of either the red reflected light which is the reflected light of the red wavelength band, the green reflected light which is the reflected light of the green wavelength band, or the blue reflected light which is the reflected light of the blue wavelength band. It has a control unit that determines the condition of the skin based on the light intensity.
The control unit selects the reflected light to be used from the red reflected light, the green reflected light, or the blue reflected light for each assumed skin condition.
The skin condition to be determined is due to a pressure sore, and only the red reflected light is used when detecting the initial symptom of the pressure sore, and the red color is used when determining the skin condition in which the symptom of the pressure sore has progressed. Use only reflected light and the blue reflected light
A skin condition detection device characterized by this.

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