CN115266645A - Excrement device with urine sugar detection function - Google Patents

Abstract

The invention provides a excreta device with urine sugar detection function, which comprises a urine accommodating groove formed on the inner side wall of a device body, and a measuring module arranged at the bottom of the urine accommodating groove and provided with an inner space; in the internal space, a light-transmitting mirror is tightly attached to the bottom of the urine containing groove, a rail faces to the bottom surface of the light-transmitting mirror, a driving module drives a light-emitting unit on the rail to move along with the rail, the light-emitting unit emits a detection light beam to a measuring surface of the light-transmitting mirror, a sensor receives the detection light beam reflected by the measuring surface, a processor is electrically connected with the light-emitting unit and the sensor, and the processor immediately generates urine sugar concentration data according to a light beam intensity signal of the sensor and a position of the light-emitting unit on the rail. The invention can rapidly complete the detection of the urine sugar and generate the urine sugar concentration data, and has more instantaneity compared with the prior method for detecting the urine sugar concentration by test paper.

Description

Excretion Device with Urine Glucose Detection Function

technical field

The invention relates to an excrement device, in particular to an excrement device with the function of detecting urine sugar.

Background technique

In recent years, the situation of diabetes has become serious, and the general public needs a non-invasive blood sugar detection method, which can measure the blood sugar concentration of each diabetic patient at home in real time, so as to relieve the pain of invasive blood sugar detection for diabetic patients.

Generally speaking, when the blood sugar concentration exceeds 180 milligrams per deciliter (mg/dl), sugar will appear in a person's urine, which means that a person's kidneys cannot absorb all the sugar in the body and the excessive concentration of sugar excreted in urine. This sugar excreted in the urine is called urine sugar.

At present, among the methods that use urine sugar detection instead of blood sugar detection, the enzyme method is the main method, and the glucose oxidase method is the most common. However, the test paper detection takes 30 to 60 seconds, so it is not enough to meet the immediacy of instant detection.

What's more serious is that the result of the test paper test is based on the color of the human eye to determine the concentration of urine sugar. That is to say, the human eyes of different people will interpret different results due to color differences, making the results inaccurate. In addition, the results of the test paper test are displayed in a semi-quantitative manner, that is, the result of the test paper test is to confirm which interval the urine sugar concentration is in, and cannot accurately confirm the urine sugar concentration value.

There are also troubles in the preservation of the test paper for test paper detection. Due to the different storage environments, the performance and quality of the test paper for judging urine sugar will be different, and the reliability of the test paper test will be questioned. In addition, when testing urine sugar with test strips, collecting urine in a cup is not a convenient and easy task for the general public.

Contents of the invention

In view of the above problems, the present invention provides a excrement device with a urine sugar detection function, which can collect urine without using a cup, and measure the concentration of urine sugar in a stable and real-time manner optically.

The excrement device with urine sugar detection function of the present invention includes:

A device body having an excrement holding tank and a urine holding groove; wherein, the urine holding groove is formed on an inner side wall of the excrement holding groove;

A measuring module is arranged at a bottom of the urine holding groove and has an inner space, and the measuring module includes:

A light-transmitting mirror is arranged in the inner space and has a measuring surface and a bottom surface; wherein the measuring surface of the light-transmitting mirror is closely attached to the bottom of the urine holding groove;

a rail, arranged in the inner space, and facing the bottom surface of the light-transmitting mirror;

A light-emitting unit is movably arranged on the track, and emits a detection beam to the bottom surface of the light-transmitting mirror;

a sensor, disposed in the inner space, facing the bottom surface of the light-transmitting mirror, and receiving the detection light beam reflected by the bottom surface;

a processor, disposed in the inner space, and electrically connected to the light emitting unit and the sensor;

A driving module, arranged in the inner space, connected to the light-emitting unit and electrically connected to the processor; wherein the processor controls the driving module to drive the light-emitting unit to move along the track;

Wherein, when the processor receives a start signal, the processor controls the light-emitting unit to emit the detection beam to the bottom surface of the light-transmitting mirror, and the detection beam is further reflected by the measurement surface of the light-transmitting mirror The light-transmitting mirror is emitted through the bottom surface, and the detection beam reflected by the bottom surface is received by the sensor, and the sensor generates a beam intensity signal according to the received reflected detection beam;

The processor further controls the driving module to drive the light-emitting unit to move on the track, and judges whether the beam intensity signal generated by the sensor is less than a threshold, and when the processor determines that the beam intensity signal is less than the threshold, The processor confirms a position of the light emitting unit on the track, and generates urine sugar concentration data according to the position.

The excrement device with the urine sugar detection function of the present invention detects the urine sugar concentration through the detection beam, can quickly complete the urine sugar detection and generate the urine sugar concentration data, and is more efficient than the existing method for detecting urine sugar concentration with test paper. immediacy.

Description of drawings

FIG. 1 is a schematic diagram of an embodiment of an excrement device with urine sugar detection function according to the present invention.

FIG. 2 is a cross-sectional view of the embodiment of the excrement device with urine sugar detection function of the present invention.

3 is a schematic diagram of the appearance of a measurement module of the excrement device with urine sugar detection function of the present invention.

4 is a schematic diagram of the first measurement of the measurement module of the excrement device with urine sugar detection function of the present invention.

FIG. 5 is a system block diagram of the excrement device with urine sugar detection function of the present invention.

Fig. 6 is a schematic diagram of an optical path of total internal reflection.

7 is a schematic diagram of the second measurement of the measurement module of the excrement device with urine sugar detection function of the present invention.

8 is a schematic diagram of the third measurement of the measurement module of the excrement device with urine sugar detection function of the present invention.

FIG. 9 is a data graph of the light movement degree and the change of urine sugar concentration in the excrement device with urine sugar detection function of the present invention.

FIG. 10 is a schematic diagram of another embodiment of the excrement device with urine sugar detection function of the present invention.

11 is a schematic cross-sectional view of another embodiment of the excrement device with urine sugar detection function of the present invention.

12 is a schematic cross-sectional view of another embodiment of the excrement device with urine sugar detection function of the present invention.

Detailed ways

Please refer to Fig. 1 and Fig. 2, the present invention is an excrement device 1 with urine sugar detection function, the excrement device 1 with urine sugar detection function includes a device body 2, and the device body 2 has a discharge Object carrying groove 5 and a urine containing groove 4. As shown in Figure 1 and Figure 2, in an embodiment of the excrement device 1 with urine sugar detection function of the present invention, the device body 2 is a toilet, and when the device body 2 is flushed, the urine The receiving groove 4 and the inner side wall 3 can be washed.

Please refer to FIG. 3 and FIG. 4 together, the urine receiving groove 4 is formed on an inner wall 3 of the device body 2 for collecting a urine 9 . A measuring module 6 is disposed on a bottom 7 of the urine holding groove 4 , and the measuring module 6 has an inner space 8 . In the inner space 8 , the measuring module 6 includes a light-transmitting mirror 10 , a rail 20 , a light emitting unit 30 , a sensor 40 , a processor 50 and a driving module 60 . In this embodiment, the driving module 60 is a stepping motor.

The light-transmitting mirror 10 is arranged in the internal space 8, and has a measuring surface 11 and a bottom surface 12, wherein the measuring surface 11 is closely attached to the bottom 7 of the urine holding groove 4, and the measuring The surface 11 is in close contact with the inner wall 3 so that the urine 9 cannot penetrate into the inner space 8 .

The track 20 is disposed in the inner space 8 and faces the bottom surface 12 of the transparent mirror 10 . The light emitting unit 30 is disposed on the track 20 in the inner space 8 , and movably emits a detection beam toward the bottom surface 12 of the transparent mirror 10 along the track 20 . The sensor 40 faces the bottom surface 12 of the transparent mirror 10 and is disposed in the inner space 8 , and receives the detection beam reflected by the bottom surface 12 .

In a preferred embodiment of the present invention, the bottom surface 12 of the transparent mirror 10 is an arc-shaped surface, and the arc-shaped surface faces the light emitting unit 30 and the sensor 40 . The track 20 in the preferred embodiment has the same arc as the bottom surface 12, so the detection beam moving along the track 20 can keep incident on the curved surface normally.

When the detection beam is incident on the light-transmitting mirror 10, no angle deflection will occur due to the vertical incident on the bottom surface 12, which is the result of the law of refraction (Snell's Law), and the law of refraction (Snell's Law) will be described later in the description. section to be discussed. After the detection beam is vertically incident on the light-transmitting mirror 10, at the place where the medium changes, that is, at the junction of the measurement surface 11 that is closely attached to the bottom 7 of the urine storage groove 4 and the urine 9, the There will be refraction and reflection. The refracted part of the detection beam will be produced because the medium of the urine 9 is different from that of the transparent mirror 10 , and the reflected part will be produced because the vector perpendicular to the measuring surface 11 changes direction. Taking a normal line perpendicular to the measuring surface 11 as a reference, the detection beam will generate an incident angle θ _i when it is incident, a reflection angle θ _r when it is reflected, and a refraction angle θ _t when it is refracted. The relationship between the incident angle θ _i , the reflection angle θ _r and the refraction angle θ _t and the relationship between how much of the detection beam will be refracted and how much of the detection beam will be reflected will be discussed in detail later in the specification.

The processor 50 is disposed in the inner space 8 and electrically connected to the light emitting unit 30 and the sensor 40 . The driving module 60 is disposed in the inner space 8 , connected to the light emitting unit 30 and electrically connected to the processor 50 , so that the processor 50 controls the driving module 60 to drive the light emitting unit 30 to move along the track 20 .

In detail, when the processor 50 receives a start signal, the processor 50 controls the light emitting unit 30 to emit the detection beam, so that the detection beam is directed toward the bottom surface 12 to enter the light-transmitting mirror 10 . According to a position of the light emitting unit 30 on the track 20, the processor 50 knows the amount of the light emitting unit 30 being moved by the driving module 60 according to the position, and then infers that the detection beam of the light emitting unit 30 is incident on the light emitting unit 30. Measure the angle of face 11. Next, the processor 50 generates a urine sugar concentration data within 3 seconds according to the angle of the detection beam incident on the measuring surface 11 and a beam intensity signal measured by the sensor 40 . The reason why the present invention can analyze the urine sugar concentration data in real time is because the optical method can obtain the physical information of the urine 9 from the beam intensity signal at the moment the detection beam irradiates the urine 9 to analyze the urine 9. Urine sugar concentration data.

Please refer to FIG. 5, in this preferred embodiment of the present invention, the processor 50 is electrically connected to an output unit 100, an input unit 200 and a power unit respectively provided on the device body 2 in the internal space 8. 300.

For the urine sugar concentration data, the processor 50 will further determine whether the urine sugar concentration data is greater than a warning value, and when the processor 50 judges that the urine sugar concentration data is greater than the warning value, the processor 50 will generate a The warning information is used to warn the user to pay attention to the blood glucose concentration in the body, and the warning information is output on the output unit 100 . In this preferred embodiment of the present invention, the output unit 100 can be a display to display the warning information or a buzzer to emit a sound to convey the warning information.

The input unit 200 is responsible for generating the activation signal, and when the input unit 200 generates the activation signal, the processor 50 receives the activation signal and starts to operate. In addition, the power unit 300 is responsible for generating power for the processor 50 .

Before introducing the excrement device 1 with the urine sugar detection function and how to obtain the urine sugar concentration data, the technical background of the present invention is introduced here, that is, how a light travels between two different media.

Please refer to Fig. 6, assuming that the surface of the first medium contacting the second medium is a plane, according to the law of refraction (Snell's Law), when light enters another medium from an intermediate value, the incident angle θ _i of an incident light and The relationship between the angle of refraction θ _t and a first refractive index n ₁ of a medium 1 and a second refractive index n ₂ of a medium 2 is as follows:

n ₁ ×sin(θ _i )＝n ₂ ×sin(θ _t )

Among them, when n ₁ >n ₂ and when the incident angle θ _i is a critical angle (critical angle) θ _cri :

The refraction angle θ _t must be 90 degrees to give the answer of sin(θ _t ) = 1, so when the incident light is at the critical angle θ _cri , the angle of light refraction will be 90 degrees between the medium one and the The surface of medium two travels between them. When light is reflected, the incident angle θ _i and the reflection angle θ _r must be equal in general, and it is a special case when the incident light is at the critical angle θ _cri .

Further, the amount of refraction and reflection of the detection beam can be discussed according to Fresnel equations. According to Fresnel equations, the reflectance R and the transmittance T are percentages, which can represent the refraction amount of the detection beam and the reflection amount of the detection beam, and the reflectance R plus the transmittance T will be equal to 1. The polarization state of the incident light can be divided into S polarization and P polarization, wherein the polarization state perpendicular to the plane is the S polarization state, and the polarization state parallel to the plane is the P polarization state. The incident light is composed of a random ratio of S-polarized light and P-polarized light in the state of no polarization, and according to the Fresnel equation, the reflectance R and transmittance T of S-polarized light and P-polarized light can be calculated in detail written as:

T _S =1-R _S

T _P =1-R _P

When θ _t = π/2, cos(θ _t = π/2) = 0, so the Fresnel equation can be simplified as:

T _S =1-R _S =1-1=0

T _P =1-R _P =1-1=0

Therefore, no matter which polarization state the incident light is in, and no matter how many ratios of S-polarized light and P-polarized light the incident light is composed of, the results obtained for S-polarized light and P-polarized light are consistent, that is to say, at θ _i = When θ _cri and θ _t = π/2, not only the incident light will travel along the plane between the medium 1 and the medium 2, but also has been regarded as total internal reflection in mathematics, because R Both _S and R _P are 1.

When θ _i <θ _cri , the incident light will continue to be totally internally reflected, that is, all the light will be reflected, R _S and R _P remain 1, T _S and T _P maintain 0, and the reflection angle θ _r is as In general, it will be equal to the incident angle θ _i .

When θ _i =θ _cri , the incident light will travel along the plane between the first medium and the second medium, and the reflected light will not be reflected in the direction of the reflection angle θ _r , because when θ _t = When π/2, the incident angle θ _i can also be regarded as θ _i = π/2 in mathematics, that is, a light parallel to the plane makes cos(θ _i = π/2) = 0, and thus we get Same _RS and R _P results:

To put it another way, because the light travels along the plane between the medium 1 and the medium 2, strictly speaking, it does not cross the plane, so there is no reflection phenomenon that occurs during general reflection, so θ _i = θ _cri ≠θ _r is a special case.

In the present invention, the plane discussed in FIG. 6 is the measurement surface 11, the incident light is the detection beam, and the _first refractive index n1 corresponds to the refractive index of the transparent mirror 10, and the second The refractive index n ₂ corresponds to the refractive index of the urine 9 . Wherein, the refractive index of the transparent mirror 10 is a known value, and the refractive index of the urine 9 is a value to be measured.

Referring to Fig. 4, Fig. 7 and Fig. 8, based on the above, it can be known that the sensor 40 in this preferred embodiment of the present invention will see the following situation when sensing the detection beam:

As shown in FIG. 4, when the incident angle _θi >the critical angle _θcri , a small part of the detection beam will be reflected into the sensor 40;

As shown in FIG. 7, when the incident angle _θi =the critical angle _θcri , all the detection light beams will travel between the planes due to total internal reflection, and because the sensor 40 is not between the planes Therefore, most of the detection beams cannot be reflected into the sensor 40, so the beam intensity signal measured by the sensor 40 will be weakened;

As shown in FIG. 8, when the incident angle _θi <the critical angle _θcri , all the detection beams will be reflected into the sensor 40 due to total internal reflection, so the beam intensity signal measured by the sensor 40 will enhance.

It can be seen that, when the incident angle θ _i is equal to the critical angle θ _cri , the beam intensity signal sensed by the sensor 40 will be smaller than the beam intensity signals at other incident angles θ _i . Conversely, when the sensor 40 senses that the light beam intensity signal is a minimum value as the incident angle θ _i changes, the angle at which the minimum value appears is the corresponding critical angle θ _cri . According to the law of refraction, the critical angle θ _cri is:

n ₁ ×sin(θ _cri )=n ₂ ×1

The present invention can use the change of the incident angle _θi to correspond to the change of the beam intensity signal measured by the sensor 40, and find out the corresponding critical angle θ _cri from the beam intensity signal sensed by the sensor 40, and from The critical angle θ _cri calculates the refractive index of the urine 9 , and then finds a urine sugar concentration corresponding to the urine 9 from the refractive index of the urine 9 , and finally makes the processor 50 generate the urine sugar concentration data.

The present invention is provided with an adjustable threshold, that is, when the processor 50 judges that the light beam intensity signal is less than the threshold, the processor 50 judges the moving position of the light emitting unit 30 on the track 20 and the detection beam incident on the The angle of the measuring surface 11 is the location where the total internal reflection of the detection beam occurs, and the current incident angle θ _i is determined to be the critical angle θ _cri .

In addition, when the processor 50 determines that the beam intensity signal is less than the threshold, the processor 50 further determines whether the beam intensity signal is a relatively low value. That is to say, after the processor 50 determines that the beam intensity signal is less than the threshold, the processor 50 continues to control the sensor 40 to continue measuring and the processor 50 continues to control the light-emitting unit 30 on the track 20 to continue to move, Until the beam intensity signal measured by the sensor 40 changes from weakening to strengthening. When the beam intensity signal changes from weakening to increasing, the beam intensity signal will have the relatively low value, and the relatively low value can more accurately enable the processor 50 to judge that the light emitting unit 30 is moving on the track 20 The position of the critical angle θ _cri occurs when . The beam intensity signal will change from weakening to increasing because the beam intensity signal will weaken when the detection beam just undergoes total internal reflection, and the beam intensity signal will continue to be full after the detection beam exceeds the critical angle θ _cri Enhanced during internal reflection, please refer to the previous explanations in Figure 4, Figure 7 and Figure 8 for details.

After the processor 50 judges that the beam intensity signal is the relatively low value, the processor 50 ends the measurement work of the light emitting unit 30 and the sensor 40, because the processor 50 has enough information to calculate the critical angle θ The angle of the _crest . After judging that the beam intensity signal is less than the threshold and judging that the beam intensity signal is the relatively low value, the processor 50 can determine the critical angle θ _cri , and the processor 50 further calculates the urine sugar concentration.

Please refer to FIG. 9 , it can be seen from the graph of the experimental data that the glucose content added in the urine 9 has a linear relationship with the degree of movement of the light-emitting unit, in other words, the urine sugar concentration and the movement of the light-emitting unit 30 The degree has a linear relationship. There is a linear relationship between the degree of movement of the light emitting unit 30 and the variation of the incident angle θ _i and the movement of the driving module 60 . Therefore, this figure can also illustrate that there is a linear relationship between the urine sugar concentration and the variation of the incident angle θ _i . Also because of this linear relationship, the excrement device 1 with urine sugar detection function of the present invention can measure the urine sugar concentration optically, that is, the above-mentioned variation of the incident angle θ _i corresponds to the sensor Find out the corresponding critical angle θ _{cri from the beam intensity signal of 40, and calculate the refractive index of the urine 9 from the critical angle θ cri ,} and then linearly correspond to the urine sugar concentration from the refractive index of the urine 9 , finally causing the processor 50 to generate the urine sugar concentration data. In this embodiment, the unit of the movement degree (au) of the light emitting unit 30 is, for example, millimeter (mm), radian (rad), and angle (°), but it is not limited thereto. In addition, the degree of movement of the light emitting unit 30 and the variation of the incident angle θ _i still maintain a linear relationship.

As can be seen in Fig. 9, the position of the urine sugar concentration of 180 milligrams per deciliter (mg/dl) corresponds to the position of the degree of movement of the light emitting unit from 5 to 5.25 a.u. Sugar will appear in urine, so the scope of application of the present invention has reached the designed urine sugar detection range, and the urine sugar concentration of the urine 9 can be detected as soon as sugar appears in a person's urine. Moreover, the present invention can better distinguish the urine sugar concentration difference between the urine sugar concentration of 50 mg/dl and the urine sugar concentration of 100 mg/dl, and is more accurate in urine sugar measurement than conventional urine sugar test paper.

When the urine holding groove 4 of the present invention is washed, the moisture remaining in the urine holding groove 4 is an average quantitative amount, and the processor 50 can take it into account when calculating the urine sugar concentration. And calculate the average quantity of residual moisture to calibrate the result of measuring the urine sugar concentration, so that the measurement of the urine sugar concentration will not be affected by the reset of the detection environment.

Please refer to FIG. 10 , in another embodiment of the present invention, the bottom surface 12A of the light-transmitting mirror 10A includes a light incident surface 121A and a light exit surface 122A, and the light incident surface 121A and the light exit surface 122A are respectively It is a plane, and the light incident surface 121A faces the light emitting unit 30 , while the light output surface 122A faces the sensor 40 . As the track 20 moves, the light-emitting unit 30 can still change the incident angle θ _i of the detection beam to measure the urine sugar concentration, and when it enters the light-incident surface 121A and reflects the light-exit surface 122A, the detection The angle change of the light beam can be included in the calculation by the processor 50, so that the sensor 40 finally generates the urine sugar concentration data in the same way.

Please refer to FIG. 11 , in another embodiment of the present invention, the device body 2 is a urinal. The urinal also includes a waste holding tank 5A and a urine receiving groove 4A formed on an inner wall 3A of the urinal. The measurement module 6 is also installed in the urine storage groove 4A of the inner wall 3A of the urinal, so as to collect the urine 9 in the urine storage groove 4A to measure the urine sugar concentration.

Please refer to FIG. 12 , in another embodiment of the present invention, the device body 2 is a squat toilet. The squatting toilet includes a waste holding tank 5B and a urine holding groove 4B formed on an inner platform 3B of the squatting toilet. The measuring module 6 is set in the urine holding groove 4B of the inner platform 3B of the squatting toilet, and the urine holding groove 4B can remain in the urine holding groove 4B after being flushed. The amount of water and the amount of water remaining on the inner platform 3B is another average ration after each flush. When calculating the urine sugar concentration, the processor 50 of the measurement module 6 can consider and calculate the other average quantity of residual moisture to calibrate the result of measuring the urine sugar concentration.

In this preferred embodiment of the present invention, the volume of the urine holding groove is not less than 0.5 milliliters, so as to produce enough thick urine 9 to block the external light-emitting unit outside the urine holding groove 4 from interfering with the measurement results , and generate sufficient urine sample volume to enhance the accuracy of the measurement of the urine sugar concentration.

In addition, in another embodiment of the present invention, the light-emitting unit 30 can be a plurality of light-emitting diodes (LEDs) or a laser diode (laser diode; LD), so as to generate the directional detection beam. And the sensor 40 can be a plurality of photodiodes (photodiodes), a spectrometer (spectrometer), a photosensitive coupled device sensor (Charge-coupled Device sensor; CCD sensor) or a complementary metal oxide semiconductor sensor (Complementary Metal-Oxide-Semiconductor sensor) ; CMOS sensor), the wavelength of the light-emitting unit 30 can be selected to select the most suitable corresponding sensor 40 .

Claims (10)

1. An excreta device having a urine sugar detection function, comprising:

a device body, which is provided with an excrement bearing groove and a urine containing groove; wherein, the urine holding groove is formed on an inner side wall of the excrement bearing groove;

a measuring module set in the bottom of the urine holding groove and having an inner space, and the measuring module includes:

a light-transmitting mirror arranged in the inner space and having a measuring surface and a bottom surface; wherein the measuring surface of the light-transmitting mirror is tightly attached to the bottom of the urine accommodating groove;

a track disposed in the interior space and facing the bottom surface of the transparent mirror;

the light-emitting unit is movably arranged on the track and emits a detection light beam to the bottom surface of the light-transmitting mirror;

a sensor disposed in the inner space, facing the bottom surface of the transparent mirror, and receiving the detection light beam reflected by the bottom surface;

the processor is arranged in the inner space and electrically connected with the light-emitting unit and the sensor;

a driving module set in the inner space and connected to the light emitting unit and the processor; wherein the processor controls the driving module to drive the light-emitting unit to move along the track;

when the processor receives a starting signal, the processor controls the light-emitting unit to emit the detection light beam to the bottom surface of the light-transmitting mirror, the detection light beam is reflected by the measuring surface of the light-transmitting mirror and then further emitted out of the light-transmitting mirror through the bottom surface, the sensor receives the detection light beam reflected out of the bottom surface, and the sensor generates a light beam intensity signal according to the received reflected detection light beam;

the processor further controls the driving module to drive the light-emitting unit to move on the track and judges whether the light beam intensity signal generated by the sensor is smaller than a threshold value;

when the processor judges that the light beam intensity signal is smaller than the threshold value, the processor confirms a position of the light-emitting unit on the track and generates urine glucose concentration data according to the position.

2. The device of claim 1, wherein the bottom surface of the transparent mirror comprises an incident surface and an emergent surface;

the light incident surface and the light emitting surface are respectively a plane, the light incident surface faces the light emitting unit, and the light emitting surface faces the sensor.

3. The device as claimed in claim 1, wherein the bottom surface of the transparent mirror is an arc-shaped surface; the curved surface faces the light emitting unit and the sensor.

4. The device of any of claims 1-3, wherein when the processor determines that the beam intensity signal is less than the threshold value, the processor further determines whether the beam intensity signal is a relatively low value;

when the light beam intensity signal is the relatively low value, the processor confirms the position of the light-emitting unit on the track and generates the urine glucose concentration data according to the position.

5. The excreta device with urine sugar test function according to any one of claims 1 to 3, further comprising:

the output unit is electrically connected with the processor and arranged on the device body; wherein the processor further determines whether the urine glucose concentration data is greater than a warning value, and when the processor determines that the urine glucose concentration data is greater than the warning value, the processor generates a warning message and outputs the warning message at the output unit;

an input unit electrically connected with the processor, arranged on the device body and used for generating the starting signal; when the input unit generates the starting signal, the processor receives the starting signal;

and the power unit is electrically connected with the processor, is arranged on the device body and generates power to provide the processor.

6. The device of claim 5, wherein the output unit is a display or a buzzer.

7. The excreta device with a urine sugar test function of any one of claims 1 to 3 wherein the volume of the urine receiving recess is not less than 0.5 ml.

8. The device according to any one of claims 1 to 3, wherein the device body is a toilet, a squat toilet, or a urinal.

9. The device as claimed in any one of claims 1 to 3, wherein the light emitting unit is a plurality of light emitting diodes or a laser diode.

10. The device as claimed in any one of claims 1 to 3, wherein the sensor is a plurality of photodiodes, a spectrometer, a CCD sensor or a CMOS sensor.

Images