TW201344176A - Apparatus and method for non-invasive blood glucose monitoring and method for analysing biological molecule - Google Patents

Abstract

An apparatus and a method for non-invasive blood glucose monitoring and a method for analysing biological molecule are provided. An apparatus for non-invasive blood glucose monitoring includes following elements. A light source generates at least one ray of light. A beam splitter with a focusing function leads the light generated from the light source into an eyeball and focuses on the eyeball. A set of photo detectors measures optical rotatory distribution (ORD) information and absorption energy information of the light reflected from the eyeball and transmitted through the first beam splitter to the set of photo detectors. A processing unit receives and processes the ORD information and the absorption energy information to obtain an ORD difference and an absorption energy difference between the light emitted from the light source and the light transmitted to the set of photo detectors, and analyzes the ORD difference and the absorption energy difference to obtain a glucose information, and since the glucose information has a corresponding relationship with a blood glucose information, the blood glucose information may be read.

Description

Non-invasive blood glucose monitoring device and method and analysis of biochemical molecules law

The present disclosure relates to a blood glucose monitoring device and method, and a method for analyzing biochemical molecules, and more particularly to a non-invasive blood glucose monitoring device and method and a method for analyzing biochemical molecules.

Diabetes is a clinical syndrome caused by factors such as absolute or relative deficiency of insulin in the body, abnormal secretion time, impaired insulin action or resistance. If diabetes is not well controlled, it can cause acute complications such as hypoglycemia, ketoacidosis, and non-keto hyperosmolar coma. Serious long-term complications include cardiovascular disease, chronic renal failure, retinopathy, neuropathy, and microvascular disease.

For diabetics, it is important to monitor blood glucose from time to time. The primary goal of managing diabetes is to maintain normal blood sugar levels. If the patient can pay attention to the control of blood sugar on weekdays, it will effectively prevent the above complications.

At present, diabetes patients often use blood glucose machines for blood glucose monitoring. However, before using the blood glucose meter to measure the blood glucose concentration value, the blood sampling step must be performed. Fingertip blood collection is an invasive (destructive) sampling method, which is complicated and causes pain, which is also the most important factor affecting diabetes patients' ability to monitor blood glucose on their own.

Therefore, the non-invasive blood glucose detection method has become a major development trend of blood glucose detection. Current non-invasive blood glucose meters use a single method for measurement, such as acoustics, optics, and electricity. But they all measure the blood sugar of human skin. the Lord. However, the structure of the skin can be divided into epidermis, dermis, and subcutaneous tissue, and various tissues, blood vessels, and water in the skin generate a variety of scattered light and absorbed light, thereby affecting the measurement of the signal, thereby affecting the judgment of the blood sugar level.

The present disclosure provides a non-invasive blood glucose monitoring device that accurately measures blood glucose information.

The present disclosure provides a portable mobile device with non-invasive blood glucose monitoring functionality that can be used in an indoor or outdoor environment.

The present disclosure provides a non-invasive blood glucose monitoring method that can continuously and instantaneously obtain a blood glucose level of a measurement subject.

The present disclosure provides a method for analyzing biochemical molecules, which can obtain a target molecule concentration when a target molecule and an interfering molecule are simultaneously present.

The present disclosure provides a non-invasive blood glucose monitoring device including at least one light source, a first beam splitter, a photodetector group, and a processing unit. The light source emits at least one light. The first beam splitter has a focusing function that causes light emitted by the light source to be incident by the first beam splitter and focused into the eyeball. The photodetector group measures the optical information and the absorbed energy information of the light reflected by the eyeball and transmitted to the photodetector group by the first beam splitter. The processing unit receives and processes the optical rotation information and the absorption energy information to obtain an optical rotation change and an absorption energy change between the light emitted by the light source and the light transmitted to the photodetector group, and analyzes the optical rotation change and the absorbed energy change. To obtain biochemical molecular information of biochemical molecules, biochemical molecules include at least glucose, and the processing unit obtains glucose information by biochemical molecular information, due to glucose information Correspondence with blood sugar information, and then read blood sugar information.

The present disclosure provides a portable mobile device having a non-invasive blood glucose monitoring function, including a device body, at least one light source, an optical kit, a photodetector group, and a processing unit. The light source emits at least one light. The optical package is mounted on the device body and includes a first beam splitter therein. The first beam splitter has a focusing function, so that the light emitted by the light source is incident by the first beam splitter and is focused into the eyeball. The photodetector group measures the optical information and the absorbed energy information of the light reflected by the eyeball and transmitted to the photodetector group by the first beam splitter. The processing unit is disposed in the device body, and receives and processes the optical information and the absorbed energy information to obtain an optical rotation change and an absorption energy change between the light emitted by the light source and the light transmitted to the photodetector group to obtain biochemistry. The biochemical molecular information of the molecule, the biochemical molecule includes at least glucose, and the processing unit obtains the glucose information by biochemical molecular information, and the glucose information has a corresponding relationship with the blood glucose information, thereby reading the blood sugar information.

The present disclosure proposes a non-invasive blood glucose monitoring method comprising the following steps. At least one light is emitted by at least one light source. The light emitted by the light source is incident by the first beam splitter having a focusing function and is focused into the eyeball. The light reflected by the eyeball is transmitted to the photodetector group by the first beam splitter. The optical detector information is used to measure the optical information and the absorbed energy information of the light transmitted to the photodetector group. The optical rotation and the absorbed energy change between the light emitted by the light source and the light transmitted to the photodetector group are obtained by processing the optical rotation information and absorbing the energy information. Analysis of changes in optical rotation and absorption energy to obtain biochemical molecular information of biochemical molecules The biochemical molecular information obtains the glucose information, and since the glucose information has a corresponding relationship with the blood glucose information, the blood glucose information is read through the corresponding relationship.

The present disclosure proposes a method for analyzing biochemical molecules, including the following steps. Establishing at least a first polynomial equation relating the biochemical molecule to the optical rotation change and at least a second polynomial equation relating the biochemical molecule to the change in absorbed energy. The biochemical molecule includes a target molecule and at least one interfering molecule, and the plurality of variables of the first polynomial equation and the second polynomial equation respectively include a target molecule concentration variable and an interference molecule concentration variable. By introducing the changes in optical rotation and absorption energy measured by the biochemical molecular monitoring device into the first polynomial equation and the second polynomial equation to calculate the target molecule when the target molecule and the interfering molecule are simultaneously present. A target molecular concentration.

Based on the above, the non-invasive blood glucose monitoring device proposed by the present disclosure can accurately measure blood glucose information. In addition, the use environment of the portable mobile device with non-invasive blood glucose monitoring function proposed in the present disclosure is not particularly limited and can be used indoors or outdoors. In addition, the non-invasive blood glucose monitoring method proposed by the present disclosure can continuously and instantaneously obtain the blood glucose level of the measurement subject. On the other hand, the analysis method of the biochemical molecule proposed by the present disclosure can obtain the target molecule concentration when the target molecule and the interfering molecule are present at the same time, and thus a more accurate target molecule concentration can be obtained.

The above and other objects and features of the present invention will become more apparent from the following description.

The purpose of the present disclosure is to provide a non-invasive blood glucose monitoring device capable of accurately measuring glucose information (eg, glucose value) of a measurement subject due to glucose information in an eyeball (eg, aqueous humor in the eyeball) ( The glucose concentration has a correspondence with the blood glucose information (blood sugar concentration), and the blood glucose information (for example, blood sugar level) is read through the correspondence.

Another object of the present disclosure is to provide a non-invasive blood glucose monitoring method that continuously and instantaneously obtains a blood glucose level of a measurement subject.

FIG. 1A is a schematic diagram of a non-invasive blood glucose monitoring device according to a first embodiment of the present disclosure. FIG. 1B is a schematic diagram of the optical rotation measuring device of FIG. 1A.

Referring to FIG. 1A, the non-invasive blood glucose monitoring device 100 includes a light source 102, a first beam splitter 104, a photodetector group 106, and a processing unit 108. The non-invasive blood glucose monitoring device 100 detects, for example, glucose in the aqueous humor 204 of the anterior chamber 202 of the eyeball 200.

Light source 102 emits light 110. The light source 102 is, for example, a light source such as a light emitting diode (LED) or a laser diode. The wavelength of the light source 102 is, for example, a glucose absorbable wavelength, that is, a wavelength that can be absorbed by glucose in the eye 200, such as a wavelength in infrared light. The light 110 emitted by the light source 102 includes linearly polarized light, circularly polarized light, elliptically polarized light or partially polarized light. In addition, the light source 102 has, for example, a function of controlling the emission frequency of the light 110, which helps the light detector 106 group determine the light to be measured by the transmission frequency. In addition, the light source 102 has a function of controlling the intensity of the light 110, for example, to ensure that the light energy entering the eyeball 200 does not cause damage. In addition, the light source 102 has, for example, an opening time for controlling the light 110. The length, the function of controlling the length of the closing time of the light 110, or a combination thereof, on the one hand provides the time for glucose detection, and on the other hand ensures that the light energy entering the eye 200 does not cause harm. In this embodiment, although the single light source 110 emits a single light 110 as an example, the disclosure is not limited thereto. In another embodiment, the type of the light source 102 and the type of the light ray 110 may be two or more.

The first beam splitter 104 has a focusing function that causes the light 110 emitted by the light source 102 to be incident by the first beam splitter 104 and focused into the eyeball 200. The first beam splitter 104, for example, focuses the light 110 onto the anterior chamber 202 of the eye 200, and the light reflected by the light 110 through the eye 200 includes reflected light from the aqueous humor 204. The first beam splitter 104 is, for example, an optical film, a lens, a grating or a diffractive optical element or a combination of any of the above.

The photodetector group 106 measures the optical information and the absorbed energy information of the light 110 reflected by the eyeball 200 and transmitted to the photodetector group 106 by the first beam splitter 104. In this embodiment, the photodetector set 106 includes an optical rotation measuring device 112 and an energy measuring device 114. The optical rotation measuring device 112 is configured to measure the optical rotation information of the light 110 reflected by the eyeball 200 and reflected by the first beam splitter 104, and the energy measuring device 114 is used to measure the reflection by the eyeball 200, and then Absorbed energy information of light 110 passing through first beam splitter 104.

In another embodiment, the optical rotation measuring device 112 and the energy measuring device 114 can be interchanged, that is, the optical light 110 reflected by the eyeball 200 and passed through the first beam splitter 104 can be measured by the optical rotation measuring device 112. The optical information is measured and measured by the energy measuring device 114 and reflected by the eye 200 Absorbed energy information of the light 110 reflected by the first beam splitter 104.

Referring to FIG. 1B, the optical rotation measuring device 112 includes a polarizing plate 112a and a photosensitive element 112b, wherein the light passes through the polarizing plate 112a and then to the photosensitive element 112b. The optical rotation measuring device 112 is, for example, an active optical rotation measuring device or a passive optical rotation measuring device, wherein the measuring angle of the active optical measuring device can be varied, and the measuring angle of the passive optical measuring device is fixed. The active optical rotation measuring device is, for example, an analyzer, and the analyzer can directly calculate the optical rotation information. The passive optical rotation angle measuring device calculates the optical rotation angle information by measuring the energy of the light 110 passing through the polarizing plate 112a by the photosensitive element 112b. The energy measuring device 114 is, for example, a photosensitive element such as a charge coupled device, a complementary metal oxide semiconductor sensor or a photodiode.

In addition, referring to FIG. 1A and FIG. 1B simultaneously, the non-invasive blood glucose monitoring device 100 further optionally includes at least one of a light blocking plate 113 and a light blocking plate 115. The light blocking plate 113 has a hole 113a and is assembled such that the light 110 first passes through the hole 113a of the light blocking plate 113 and is then transferred to the photosensitive member 112b. The light blocking plate 113 is disposed between the polarizing plate 112a and the photosensitive element 112b, for example, but is not intended to limit the disclosure. In other embodiments, the light barrier 113 can be further assembled such that the light 110 passes first through the polarizer 112a and through the aperture 113a of the light barrier 113. In addition, the light blocking plate 115 has a hole 115a and is assembled such that the light 110 passes through the hole 115a of the light blocking plate 115 and is then transmitted to the energy measuring device 114 (e.g., the photosensitive member). The light blocking plates 113, 115 are respectively, for example, metal reticle or quartz glass reticle. The light blocking plates 113 and 115 respectively prevent stray light from entering the optical rotation measuring device 112 and the energy measuring device 114, so that the interference of the stray light can be reduced, thereby improving the signal/ Noise ratio (S/N ratio). It should be noted that in each of the following embodiments, the influence of the stray light on the measurement result of the optical rotation measuring device and the energy measuring device can be reduced by the light blocking plate. However, in other embodiments, the description is omitted. Description of the light barrier.

Referring to FIG. 1A , the processing unit 108 is coupled to the optical rotation measuring device 112 and the energy measuring device 114 of the photodetector group 106 to receive and process the optical information and the absorbed energy information to obtain the light source 102. The optical change and the absorbed energy change between the emitted light 110 and the light 110 transmitted to the photodetector set 106, and the change of the optical change and the absorbed energy are analyzed to obtain biochemical molecular information of the biochemical molecule, and the biochemical molecule is at least Including glucose, and the processing unit obtains glucose information by biochemical molecular information. The biochemical molecule is, for example, cholesterol, uric acid, water, lactic acid, urea, ascorbic acid or a combination thereof. In addition, interfering molecules may be included in the biochemical molecule, such as molecules other than the labeled (eg, glucose), such as cholesterol, uric acid, water, lactic acid, urea, or ascorbic acid. Among them, ascorbic acid and lactic acid may interfere with the optical information, and water may interfere with the absorption of energy information. In the process of obtaining glucose information by processing unit 108, processing unit 108 may exclude interference caused by interfering molecules. The processing unit 108 can also statistically analyze the optical rotation information and absorb the energy information from the control light source variation, the optical component spatial offset or a combination thereof to obtain glucose information, and the light source change includes a change of the light emission frequency, a change of the light energy intensity, and A change in the length of the light on time, a change in the length of the light off time, or a combination thereof. Since the glucose concentration in the eyeball (eg, the aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, the corresponding relationship is System, and then read blood sugar information (such as blood sugar levels). The processing unit 108 is, for example, an analog digital circuit integration module, wherein the analog digital circuit integration module includes a microprocessor, an amplifier, and an analog digital converter. The analog digital circuit integration module can further include a wireless transmission device.

In this embodiment, processing unit 108 is coupled, for example, to light source 102 to control the optical characteristics of light 110 emitted by light source 102.

The non-invasive blood glucose monitoring device 100 further includes an optical information analyzing unit 116 for detecting light information of the light 110 from the first beam splitter 104 before the light 110 is incident on the eyeball 200, and the light can be Light information of 110 is selectively transmitted to processing unit 108 or alert 118 to provide feedback control of the optical characteristics of light 110. The optical information analysis unit 116 includes at least one of an optical power meter and a light sensor. The light information detected by the optical power meter is energy information, and the light information detected by the light sensor is energy information and location information. At least one of them. The optical properties of the light 110 are, for example, the energy of the exit and/or the position of the light.

When the emission energy of the light 110 emitted by the light source 102 is too high, the light 110 may cause damage to the eyeball 200. Therefore, when the processing unit 108 receives the energy information of the light 110 that is too high in energy emission, the processing unit 108 reduces the emission energy of the light 110 emitted by the light source 102. On the other hand, when the warning device 118 receives the energy information of the light 110 that is too high, the warning device 118 emits a warning signal such as light or sound to inform the light source of the light 110 emitted by the light source 102. High, the emission energy of the light 110 needs to be adjusted. Therefore, the optical information analyzing unit 116 can prevent the eyeball from being excessively high due to the excessive energy of the light 110. 200 causes damage.

In addition, when the position of the light ray 110 emitted by the light source 102 is shifted, the accuracy of the blood glucose measurement is lowered. Therefore, when the processing unit 108 receives the position information of the light position of the light ray 110, the processing unit 108 adjusts the light position of the light ray 110 emitted by the light source 102. On the other hand, when the warning device 118 receives the position information of the light position of the light 110, the warning device 118 emits a warning signal such as light or sound to inform the light source position of the light 110 emitted by the light source 102. An offset is generated, and the position of the light of the light 110 needs to be adjusted. Therefore, the optical information analyzing unit 116 can prevent the shift of the light position of the light 110, thereby improving the accuracy of the blood sugar measurement.

In this embodiment, the energy information detected by the optical information analyzing unit 116 is simultaneously transmitted to the processing unit 108 and the alerter 118 as an example, but the energy information is transmitted to the processing unit 108 and the alerter 118. One of them can perform the feedback control operation. For example, the optical information analysis unit 116 is coupled to the processing unit 108 and the alarm 118, but the optical information analysis unit 116, the processing unit 108, and the alarm 118 are not limited thereto.

In another embodiment, the light source 102 is coupled to a light source control unit (not shown), for example, when the light information analysis unit 116 transmits the energy information of the light 110 to the light source control unit to perform feedback control on the light source 102. .

In addition, in this embodiment, the first optical splitter 104 is detected by the optical information analyzing unit 116 before the light 110 is incident on the eyeball 200. The reflected light 110 is described as an example.

In addition, the non-invasive blood glucose monitoring device 100 further selectively includes an eye aiming positioning device 120 for aligning the line of sight 122 of the eye with the eye aiming positioning device 120 to determine the measurement position of the eyeball 200. . The eye aiming positioning device 120 is, for example, a light spot, a logo or an embossed pattern.

In another aspect, the non-invasive blood glucose monitoring device 100 more preferably includes a connecting element 124. One end of the connecting member 124 is connected to the light exit port of the non-invasive blood glucose monitoring device 100, and the other end of the connecting member 124 is for abutting against the outer edge of the eye. In addition, the non-invasive blood glucose monitoring device 100 further optionally includes a sheath 126 disposed on the side of the connecting member 124 for abutting against the outer edge of the eye. The sheath 126 is, for example, a disposable sheath.

Based on the first embodiment, in the non-invasive blood glucose monitoring device 100, the optical rotation change and the absorption energy change between the light 110 emitted by the light source 102 and the light 110 transmitted to the photodetector group 106 can be simultaneously changed. The analysis is performed, and the glucose information (for example, the glucose value) is measured, and since the glucose concentration in the eyeball (for example, the aqueous humor in the eyeball) has a correspondence relationship with the blood glucose concentration, the correspondence is read and the reading is performed with high accuracy. Blood sugar information (eg, blood sugar values).

In addition, the non-invasive blood glucose monitoring device 100 can be used for miniaturization, for example, in a headband type or in combination with glasses, thereby improving the convenience of use. In addition, the use environment of the non-invasive blood glucose monitoring device 100 is not particularly limited and can be used indoors or outdoors.

2 is a non-invasive blood glucose monitor according to a second embodiment of the present disclosure. Schematic diagram of the measuring device.

Referring to FIG. 1A and FIG. 2 of the present invention, the non-invasive blood glucose monitoring device 300 of the second embodiment is different from the non-invasive blood glucose monitoring device 100 of the first embodiment in the photodetector group of the second embodiment. The optical rotation measuring device 312 and the energy measuring device 314 in the 306 are located on the same side of the first optical splitter 104, and the optical rotation measuring device 112 and the energy measuring device 114 in the photodetector group 106 of the first embodiment respectively Located on both sides of the first beam splitter 104. The optical rotation measuring device 312 and the energy measuring device 314 are respectively coupled to the processing unit 108, respectively, but are not intended to limit the disclosure. The components, connection relationships, and functions of the other components of the non-invasive blood glucose monitoring device 300 of the second embodiment are similar to those of the non-invasive blood glucose monitoring device 100 of the first embodiment, and thus will not be described herein.

In this embodiment, the photodetector set 306 is used, for example, to measure the light 110 reflected by the eyeball 200 and reflected by the first beam splitter 104. The light 110 to be measured is, for example, first transmitted to the optical rotation measuring device 312 for measurement of the optical rotation information, and then entered into the energy measuring device 314 for measurement of the absorbed energy information. In another embodiment, the photodetector set 306 can also be used to measure the light 110 reflected by the eyeball 200 and then passed through the first beam splitter 104.

In another embodiment, the non-invasive blood glucose monitoring device 300 further includes another set of optical rotation measuring device 312 and energy measuring device 314, and has two sets of optical rotation measuring device 312 and energy measuring device 314 at the same time. The optical information and the absorbed energy information of the light 110 reflected by the eyeball 200 and passing through the first beam splitter 104 are respectively measured, and measured by the eyeball 200, The optical information and the absorbed energy information of the light 110 reflected by the first beam splitter 104 are then used.

Similarly, since the non-invasive blood glucose monitoring device 300 of the second embodiment can simultaneously analyze the optical change and the absorbed energy change between the light 110 emitted by the light source 102 and the light 110 transmitted to the photodetector group 306. And the glucose information (for example, the glucose value) is measured, and since the glucose concentration in the eyeball (for example, the aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, the blood glucose concentration is read by the correspondence relationship, thereby reading the blood glucose with high accuracy. Information (eg, blood glucose values). Further, the non-invasive blood glucose monitoring device 300 can be miniaturized, so it is quite convenient to use and can be used indoors or outdoors.

FIG. 3 is a schematic diagram of a non-invasive blood glucose monitoring device according to a third embodiment of the present disclosure.

Referring to FIG. 1A and FIG. 3 of the present invention, the non-invasive blood glucose monitoring device 400 of the third embodiment is different from the non-invasive blood glucose monitoring device 100 of the first embodiment in the non-invasive blood glucose monitoring of the third embodiment. The device 400 further includes a second beam splitter 404, and the photodetector group 406 includes a first photodetector 408 and a second photodetector 410. The components, connection relationships, and functions of the other components of the non-invasive blood glucose monitoring device 400 of the third embodiment are similar to those of the non-invasive blood glucose monitoring device 100 of the first embodiment, and thus will not be described herein.

The second beam splitter 404 transmits the light 110 reflected by the eyeball 200 and transmitted by the first beam splitter 104 to the photodetector group 406. The second beam splitter 404 is, for example, an optical film, a lens, a grating or a diffractive optical element or a combination of any of the above.

The first photodetector 408 is configured to measure the light 110 reflected by the second beam splitter 404, and the second photodetector 410 is configured to measure the light 110 passing through the second beam splitter 404. The first photodetector 408 includes an optical rotation measuring device 412 and an energy measuring device 414 , and the second optical detector 410 includes an optical rotation measuring device 416 and an energy measuring device 418 . The light 110 to be measured is, for example, first transmitted to the optical rotation measuring device 412 (or 416) for measurement of the optical rotation information, and then entered into the energy measuring device 414 (or 418) for measurement of the absorbed energy information. The components of the optical rotation measuring devices 412, 416 are similar to those of the optical rotation measuring device 112 of the first embodiment, and the components of the energy measuring devices 414, 418 and the energy measuring device 114 of the first embodiment. The composition of the device is similar, so it will not be described here. When both the first photodetector 408 and the second photodetector 410 in the non-invasive blood glucose monitoring device 400 can simultaneously measure the optical rotation information and absorb the energy information, the two groups obtained by simultaneous cross-alignment can be obtained. The optical information and the absorbed energy information are analyzed, and the optical change and the absorbed energy change between the light 110 emitted by the light source 102 and the light 110 transmitted to the photodetector group 406 are analyzed, and glucose information (eg, glucose is measured). Value), since the glucose concentration in the eyeball (for example, aqueous humor in the eyeball) has a correspondence relationship with the blood glucose concentration, the blood glucose information (for example, blood sugar level) having high accuracy is read through the correspondence. The optical rotation measuring devices 412, 416 and the energy measuring devices 414, 418 are respectively coupled to the processing unit 108, respectively, but are not intended to limit the disclosure.

It should be noted that when the optical rotation measuring devices 412, 416 are both passive optical rotation measuring devices and each includes a polarizing plate, the polarizing plate in the optical rotation measuring devices 412, 416 is, for example, one of a horizontal polarizing plate and a vertical polarizing plate. And another One, or two polarizing plates of known angles. If two sets of polarizing plates with known optical rotation angles are combined, one of the measurement methods is to compare the energy difference between the two groups. The difference in energy can be seen that the optical rotation change is in a specific glucose concentration range to improve the detection accuracy. Another method is to determine the offset component by the absorption energy change by using two sets of polarizing plates with known optical rotation angles, and then calculate the optical rotation information.

In another embodiment, one of the first photodetector 408 and the second photodetector 410 is, for example, a single optical measuring device, the first photodetector 408 and the second photodetector 410. The other of them is, for example, a single energy measuring device.

In addition, in the above embodiment, although the light 110 reflected by the second beam splitter 404 and/or the light 110 passing through the second beam splitter 404 is exemplified by a light. However, the light 110 reflected by the second beam splitter 404 and/or the light 110 passing through the second beam splitter 404 can be split into two or more rays via the second beam splitter 404, and then the first described above. The photodetector 408 and the second photodetector 410 perform measurement.

Based on the third embodiment, the non-invasive blood glucose monitoring device 400 can simultaneously analyze the optical change and the absorbed energy change between the light 110 emitted by the light source 102 and the light 110 transmitted to the photodetector group 406. Glucose information (eg, glucose value) is measured, and since the glucose concentration in the eyeball (eg, aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, the blood glucose information with high accuracy is read through the corresponding relationship ( For example, blood sugar value). Further, the non-invasive blood glucose monitoring device 400 can be miniaturized, so it is quite convenient to use and can be used indoors or outdoors.

FIG. 4 is a schematic diagram of a non-invasive blood glucose monitoring device according to a fourth embodiment of the present disclosure.

Referring to FIG. 3 and FIG. 4 of the present invention, the non-invasive blood glucose monitoring device 500 of the fourth embodiment is different from the non-invasive blood glucose monitoring device 400 of the third embodiment in the non-invasive blood glucose of the fourth embodiment. In the monitoring device 500, the photodetector group 506 includes a first photodetector 508 and a second photodetector 510, and the first photodetector 508 and the second photodetector 510 are located in the second optical splitter 404. The same side. In this embodiment, the first photodetector 508 and the second photodetector 510 are, for example, located on a side of the light beam 110 that penetrates the second beam splitter 404, and are used to measure the light beam 110 to penetrate the second splitting light, respectively. The light rays 110a, 100b generated by the device 404. One of the first photodetector 508 and the second photodetector 510 is, for example, an optical rotation measuring device for measuring optical rotation information, and the first photodetector 508 and the second photodetector 510 are used. The other of them is, for example, an energy measuring device for measuring energy absorption information. The first photodetector 508 and the second photodetector 510 are coupled to the processing unit 108, for example, but are not intended to limit the disclosure. The components, connection relationships, and functions of the other components of the non-invasive blood glucose monitoring device 500 of the fourth embodiment are similar to those of the non-invasive blood glucose monitoring device 400 of the third embodiment, and thus will not be described herein.

In another embodiment, the first photodetector 508 and the second photodetector 510 are also located on a side of the second beam splitter 404 that reflects the light 110, and are respectively used to measure the second beam splitter 404. The two rays of light generated by the reflected light 110 are reflected.

In the above embodiment, although the light reflected by the second beam splitter 404 The line 110 and/or the light 110 passing through the second beam splitter 404 is illustrated by taking two rays 110a, 100b as an example. However, the light 110 reflected by the second beam splitter 404 and/or the light 110 passing through the second beam splitter 404 can be further divided into three or more light beams by the second beam splitter 404, and the above described A photodetector 508 and a second photodetector 510 measure.

Similarly, since the non-invasive blood glucose monitoring device 500 of the fourth embodiment can simultaneously change the optical rotation and the absorption energy between the light 110 emitted by the light source 102 and the light 110a, 100b transmitted to the photodetector group 506. The analysis is performed, and the glucose information (for example, the glucose value) is measured, and since the glucose concentration in the eyeball (for example, the aqueous humor in the eyeball) has a correspondence relationship with the blood glucose concentration, the correspondence is read and the reading is performed with high accuracy. Blood sugar information (eg, blood sugar values). Further, the non-invasive blood glucose monitoring device 500 can be miniaturized, so it is quite convenient to use and can be used indoors or outdoors.

FIG. 5 is a flow chart showing a non-invasive blood glucose monitoring method according to a fifth embodiment of the present disclosure.

Referring to FIG. 5, firstly, step S90 may be selectively performed to aim the eyeball at the eye aiming positioning device for aligning the line of sight of the eye with the positioning device for eye aiming, and the alignment includes the optical axis of the device. The relative angle and position of the eye's line of sight are adjusted to determine the measurement position of the eye. Then, in step S100, at least one light is emitted by at least one light source. Then, step S102 can be selectively performed to control the optical characteristics of the light source, the spatial offset of the optomechanical component, or a combination thereof, which can be used to generate a change factor, and help to analyze more accurate blood glucose information. Among them, the light can be controlled by the light source The transmission frequency, intensity, length of turn-on time, length of turn-off time, or a combination thereof. The photodetector group can determine the light to be measured by the transmission frequency. In addition, by controlling the intensity of the light source by the light source, it is ensured that the light energy entering the eyeball does not cause damage. In addition, by controlling the length of the light, the length of the closing time, or a combination thereof, the light source can provide the time for glucose detection, and on the other hand, ensure that the light energy entering the eyeball does not cause damage. Then, step S104 is selectively performed to detect light information of the light from the first beam splitter before the light is incident on the eyeball to perform feedback control on the optical characteristics of the light. The light information includes at least one of energy information and location information. Optical properties are, for example, emission energy and/or light position. Next, step S106 is performed to cause the light emitted by the light source to be incident and focused into the eyeball by the first beam splitter having the focusing function. Then, one of step S108 and step S110 can be performed. Step S108 is to transmit the light reflected by the eyeball to the photodetector group by the first beam splitter. In step S110, the light reflected by the eyeball is transmitted to the second beam splitter by the first beam splitter, and then transmitted to the photodetector group by the second beam splitter. Furthermore, in step S112, the optical detector group measures the optical rotation information and the absorbed energy information of the light transmitted to the photodetector group. Then, in step S114, the optical rotation and the absorbed energy change between the light emitted by the light source and the light transmitted to the photodetector group are obtained by processing the optical rotation information and the absorption energy information. Next, step S116 is performed to analyze the change of the optical rotation and the change of the absorbed energy to obtain biochemical molecular information of the biochemical molecule, the biochemical molecule includes at least glucose, and the glucose information is obtained by biochemical molecular information, because the eyeball (for example, the room in the eyeball) In water) The glucose concentration has a corresponding relationship with the blood glucose concentration, and the blood glucose information (for example, blood sugar level) is read through the correspondence. Biochemical molecules such as cholesterol, uric acid, water, lactic acid, urea, ascorbic acid or a combination thereof. In addition, interfering molecules may be included in the biochemical molecule, such as molecules other than the labeled (eg, glucose), such as cholesterol, uric acid, water, lactic acid, urea, or ascorbic acid. Among them, ascorbic acid and lactic acid may interfere with the optical information, and water may interfere with the absorption of energy information. Will interfere with the absorption of energy information. Further, in step S116, interference caused by the interfering molecules is more selectively excluded. Various aspects and various use devices of the various non-invasive blood glucose monitoring methods of the fifth embodiment have been described in detail in the first to fourth embodiments, and thus will not be described again.

Based on the above, the non-invasive blood glucose monitoring method proposed in the fifth embodiment is to measure the glucose information (eg, glucose value) of the measurement object by optically detecting the eyeball, and thus can be obtained continuously and instantaneously. The glucose information (eg, glucose concentration) of the subject is measured, and since the glucose concentration has a correspondence with the blood glucose concentration, blood glucose information (eg, blood glucose level) can be read.

On the other hand, the non-invasive blood glucose monitoring device of the above embodiment is more applicable to the portable mobile device, and the portable mobile device has a non-invasive blood glucose monitoring function. Portable mobile devices are, for example, mobile phones, tablet computers, and digital cameras. Hereinafter, a portable mobile device having a non-invasive blood glucose monitoring function will be described by way of example.

FIG. 6 illustrates a non-invasive blood of a sixth embodiment of the present disclosure. Schematic diagram of a portable mobile device for sugar monitoring functions.

Referring to FIG. 2 and FIG. 6 simultaneously, the portable mobile device 600 of the sixth embodiment is different from the non-invasive blood glucose monitoring device 300 of the second embodiment in that the portable mobile device 600 further includes the device body 602 and the optical device. Kit 604. The optical package 604 is mounted on the device body 602, and the optical package 604 includes a first beam splitter 104. The photodetector group 606, the processing unit 108, the light source 102, the optical information analyzing unit 116, and the alerter 118 are disposed in the body 602, for example, but are not intended to limit the disclosure. In addition, the photodetector group 606 includes an optical rotation measuring device 612 and an energy measuring device 614, wherein the portable mobile device 600 uses the photosensitive element in the camera module as the energy measuring device in the photodetector group 606. 614. The optical rotation measuring device 612 and the energy measuring device 614 are respectively coupled to the processing unit 108, but are not intended to limit the disclosure. The optical rotation measuring device 612 is, for example, an active optical rotation measuring device or a passive optical rotation measuring device. The energy measuring device 614 is, for example, a photosensitive element such as a charge coupled device, a complementary metal oxide semiconductor sensor, or a photodiode. In addition, the light source 110 for performing blood glucose monitoring by the portable mobile device 600 is transmitted by using a light travel route in the camera module of the portable mobile device 600. The components, connection relationships, and functions of the other components of the portable mobile device 600 of the sixth embodiment are similar to those of the non-invasive blood glucose monitoring device 300 of the second embodiment, and in the sixth embodiment and the second embodiment. Similar components are similar components, and the monitoring method of blood glucose can be referred to the second embodiment, and thus will not be described again.

In addition, in the sixth embodiment, one end of the connecting component 124 connecting component is connected to the light exit port 601 of the portable mobile device 600, and the connecting component 124 The other end is used to abut the outer edge of the eye.

In another aspect, optical kit 604 can more optionally include lens set 608. When the optical kit 604 has the lens set 608, the optical kit 604 can be integrated into the lens in the camera module of the portable mobile device 600. Moreover, regardless of whether the optical kit 604 has the lens set 608, the lens in the camera module of the portable mobile device 600 can be replaced with an optical kit 604 for blood glucose monitoring. In another embodiment, when the blood glucose monitoring is performed, with the design of the light source, the optical package 604 can be directly attached to the lens in the camera module of the portable mobile device 600.

In this embodiment, light 110 emitted by light source 102 is incident by the first beam splitter 104 and focused into eye 200. The photodetector set 606 is, for example, used to measure the light 110 reflected by the eyeball 200 and passed through the first beam splitter 104. The light 110 to be measured is, for example, first transmitted to the optical rotation measuring device 612 for measurement of the optical rotation information, and then entered into the energy measuring device 614 for measurement of the absorbed energy information.

Based on the above, the portable mobile device 600 of the sixth embodiment can simultaneously analyze the optical change and the absorbed energy change between the light 110 emitted by the light source 102 and the light 110 transmitted to the photodetector group 606. The glucose information (eg, glucose value) is measured, and the glucose concentration in the eyeball (eg, the aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, and the blood glucose information with high accuracy is read through the corresponding relationship. (eg, blood sugar value). In addition, since the blood glucose monitoring function is integrated into the portable mobile device 600, it is quite convenient in use. In addition, the mobile device 600 can be connected to the cloud by using a program or network of the portable mobile device 600 to provide telemedicine. Care.

FIG. 7 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to a seventh embodiment of the present disclosure.

Referring to FIG. 6 and FIG. 7 simultaneously, the portable mobile device 700 of the seventh embodiment is different from the portable mobile device 600 of the sixth embodiment in that the portable mobile device 700 of the seventh embodiment further includes The second optical splitter 404 (refer to the third embodiment), and the photodetector set 606 further includes an optical rotation measuring device 616 and an energy measuring device 618. The optical rotation measuring device 616 is, for example, an active optical rotation measuring device or a passive optical rotation measuring device. The energy measuring device 618 is, for example, a photosensitive element such as a charge coupled device, a complementary metal oxide semiconductor sensor, or a photodiode. The components, connection relationships, and functions of the other components of the portable mobile device 700 of the seventh embodiment are similar to those of the portable mobile device 600 of the sixth embodiment, and the seventh embodiment is similar to the sixth embodiment. The components are similar components, and the monitoring method of blood glucose can refer to the third embodiment, and thus will not be described herein.

The second beam splitter 404 transmits, for example, the light 110 reflected by the eyeball 200 and transmitted by the first beam splitter 104 to the photodetector group 606. The second beam splitter 404 is, for example, an optical film, a lens, a grating or a diffractive optical element or a combination of any of the above.

In the photodetector set 606, the optical rotation measuring device 612 and the energy measuring device 614 are used, for example, to measure the light 110c reflected by the eyeball 200 and passed through the first beam splitter 104. The light 110c to be measured is, for example, first transmitted to the optical rotation measuring device 612 for measurement of the optical rotation information, and then entered into the energy measuring device 614 for measurement of the absorbed energy information. Optical rotation measurement The device 616 and the energy measuring device 618 are used, for example, to measure the light 110d reflected by the eyeball 200, transmitted to the second beam splitter 404 via the first beam splitter 104, and reflected by the second beam splitter 404. The light 110d to be measured is, for example, first transmitted to the optical rotation measuring device 616 for measurement of the optical rotation information, and then entered into the energy measuring device 618 for measurement of the absorbed energy information.

In this embodiment, the energy measuring devices 614, 618 are illustrated in two separate components. However, in another embodiment, the energy measuring devices 614, 618 can also be different sensing regions on the same photosensitive element, and the sensing of the light can be performed using different sensing regions on the photosensitive member.

Similarly, the portable mobile device 700 of the seventh embodiment can simultaneously analyze the optical change and the absorbed energy change between the light 110 emitted by the light source 102 and the light 110c, 110d transmitted to the photodetector group 606. And the glucose information (for example, the glucose value) is measured, and since the glucose concentration in the eyeball (for example, the aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, the blood glucose concentration is read by the correspondence relationship, thereby reading the blood glucose with high accuracy. Information (eg, blood glucose values). In addition, since the blood glucose monitoring function is integrated into the portable mobile device 700, it is quite convenient in use. In addition, the mobile device 700 can be connected to the cloud using a program or network of the portable mobile device 700 to provide remote medical care.

FIG. 8 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to an eighth embodiment of the present disclosure.

Referring to FIG. 7 and FIG. 8 simultaneously, the portable mobile device 800 of the eighth embodiment differs from the portable mobile device 700 of the seventh embodiment in that, in the portable mobile device 800, the light 110 passes through the first a beam splitter 104 Two rays 110e, 110f can be generated, so there is no second beam splitter 404 in the portable mobile device 700. In addition, the photodetector set 606 of the portable mobile device 800 has only one energy measuring device 614 without the energy measuring device 618. The energy measurement device 614 includes sensing regions 614a, 614b that can measure the absorbed energy information of the light rays 110e, 100f, respectively. The components, connection relationships, and functions of the other components of the portable mobile device 800 of the eighth embodiment are similar to those of the portable mobile device 700 of the seventh embodiment, and the eighth embodiment is similar to the seventh embodiment. The components are similar components, and the monitoring method of blood glucose can refer to the seventh embodiment, and thus will not be described again.

In this embodiment, the light rays 110e, 100f are measured by the same energy measuring device 614. However, in another embodiment, the portable mobile device 800 can also measure the light rays 110e, 100f using two separate energy measuring devices.

It should be noted that, in the above embodiment, the light 110 is illustrated as being divided into two light rays 110e and 100f through the first beam splitter 104, but is not intended to limit the disclosure. Referring to the above embodiments, those skilled in the art can understand that when the light ray 110 is split into two or more light beams by the first beam splitter 104, the number of sensing regions on the energy measuring device 614 can be divided into two or more. And corresponding to the light from the first beam splitter 104, respectively, and can separately measure the absorbed energy information of the corresponding light.

Although, in this embodiment, more than two rays of light received by the energy measuring device 614 are generated via the first beam splitter 104, it is not intended to limit the disclosure. In another embodiment, by the energy measuring device 614 The light received by the light source 100 can also be formed by the light source 100. Therefore, the light passing through the first beam splitter 104 can be two or more. The number of sensing regions on the energy measuring device 614 can also be divided into two or more. Instead, the light from the first beam splitter 104 can be separately measured, and the absorbed energy information of the corresponding light can be separately measured.

Similarly, the portable mobile device 800 of the eighth embodiment can simultaneously analyze the optical change and the absorbed energy change between the light 110 emitted by the light source 102 and the light 110e, 110f transmitted to the photodetector group 606. And the glucose information (for example, the glucose value) is measured, and since the glucose concentration in the eyeball (for example, the aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, the blood glucose concentration is read by the correspondence relationship, thereby reading the blood glucose with high accuracy. Information (eg, blood glucose values). In addition, since the blood glucose monitoring function is integrated into the portable mobile device 800, it is quite convenient in use. In addition, the mobile device 800 can be connected to the cloud to provide remote medical care, and the blood glucose data can be used to remind or control the medication. In case of an emergency, the medical unit can be directly notified for medical care.

FIG. 9 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to a ninth embodiment of the present disclosure.

Referring to FIG. 7 and FIG. 9 simultaneously, the portable mobile device 900 of the ninth embodiment differs from the portable mobile device 700 of the seventh embodiment in the composition and seventh implementation of the optical package 904 of the ninth embodiment. The composition of the optical kit 604 is different. The optical package 904 is externally connected to the device body 602, and the optical package 904 includes a first light splitter 104 and a lens group 608, and further includes a light source 102 and a second beam splitter 404, and more selectively The optical information analysis unit 116 and the alarm 118 are included. The components, connection relationships, and functions of the other components of the portable mobile device 900 of the ninth embodiment are similar to those of the portable mobile device 700 of the seventh embodiment, and the ninth embodiment is similar to the seventh embodiment. The components are similar components, and the monitoring method of blood glucose can refer to the seventh embodiment, and thus will not be described again.

Similarly, the portable mobile device 900 of the ninth embodiment can simultaneously analyze the optical change and the absorbed energy change between the light 110 emitted by the light source 102 and the light 110c, 110d transmitted to the photodetector group 606. And the glucose information (for example, the glucose value) is measured, and since the glucose concentration in the eyeball (for example, the aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, the blood glucose concentration is read by the correspondence relationship, thereby reading the blood glucose with high accuracy. Information (eg, blood glucose values). In addition, since the blood glucose monitoring function is integrated into the portable mobile device 900, it is quite convenient in use. In addition, remote medical care can be provided by connecting the cloud with the program or network of the portable mobile device 900.

It is to be noted that the concept of the external optical package 904 in the portable mobile device 900 of the ninth embodiment can also be applied to the sixth to eighth embodiments.

FIG. 10 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to a tenth embodiment of the present disclosure.

Referring to FIG. 6 and FIG. 10 simultaneously, the portable mobile device 1000 of the tenth embodiment is different from the portable mobile device 600 of the sixth embodiment in the composition and the sixth implementation of the optical package 1004 of the tenth embodiment. The composition of the optical kit 604 is different. Optical kit 1004 is externally connected to a portable mobile device The lens 1006 is disposed on the lens 1006, and the optical package 1004 includes a first beam splitter 104, a light source 102, and an optical rotation measuring device 612, and further optionally includes an optical information analyzing unit 116 and a warning device 118. The light source 102, the optical rotation measuring device 612, and the optical information analyzing unit 116 can be coupled to the processing unit 108 in the most appropriate manner, and will not be described herein. The components, connection relationships, and functions of the other components of the portable mobile device 1000 of the tenth embodiment are similar to those of the portable mobile device 600 of the sixth embodiment, and the tenth embodiment is similar to the sixth embodiment. The components are similar components, and the monitoring method of blood glucose can refer to the sixth embodiment, and thus will not be described again.

When performing blood glucose measurement, the optical rotation measuring device 612 and the energy measuring device 614 are used, for example, to measure the light 110 reflected by the eyeball 200 and passed through the first beam splitter 104. The light 110 to be measured is, for example, first transmitted to the optical rotation measuring device 612 for measurement of the optical rotation information, and then passes through the lens 1006, and then enters the energy measuring device 614 for measurement of the absorbed energy information.

Similarly, the portable mobile device 1000 of the tenth embodiment can simultaneously analyze the optical change and the absorbed energy change between the light 110 emitted by the light source 102 and the light 110 transmitted to the photodetector group 606, and Glucose information (eg, glucose value) is measured, and since the glucose concentration in the eyeball (eg, aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, the blood glucose information with high accuracy is read through the corresponding relationship ( For example, blood sugar value). In addition, since the blood glucose monitoring function is integrated into the portable mobile device 1000, it is quite convenient in use. In addition, portable action is available The program or network of the device 1000 is connected to the cloud to provide remote medical care.

FIG. 11 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to an eleventh embodiment of the present disclosure.

Referring to FIG. 10 and FIG. 11 simultaneously, the portable mobile device 1100 of the eleventh embodiment differs from the portable mobile device 1000 of the tenth embodiment in that, in the portable mobile device 1100, the light 110 passes through After the first beam splitter 104, two rays 110g, 110h can be generated. In addition, the photodetector set 606 of the portable mobile device 1100 includes optical rotation measuring devices 612, 616 and an energy measuring device 614. Wherein, the energy measuring device 614 includes sensing regions 614c, 614d. The light rays 110g and 100h can measure the optical rotation information by the optical rotation measuring devices 612 and 616, respectively, and then measure the absorbed energy information by the sensing regions 614c and 614d of the energy measuring device 614, respectively. The components, connection relationships, and functions of the other components of the portable mobile device 1100 of the eleventh embodiment are similar to those of the portable mobile device 1000 of the tenth embodiment, and the eleventh and tenth embodiments The similar components are similar components, and the monitoring method of blood glucose can refer to the tenth embodiment, and thus will not be described herein.

In this embodiment, the light 110g, 100h is measured by the same energy measuring device 614. However, in another embodiment, the portable mobile device 1100 can also measure the light rays 110g, 100h using two separate energy measuring devices.

It should be noted that, in the above embodiment, the light 110 is illustrated as being divided into two light rays 110g and 100h through the first beam splitter 104, but is not intended to limit the disclosure. Common knowledge in this technical field According to the above embodiment, when the light ray 110 is split into two or more light beams by the first beam splitter 104, the number of sensing regions on the energy measuring device 614 can be further divided into two or more, and the corresponding light splitting signals are respectively corresponding to the first light splitting. The light of the device 104 can be used to measure the absorbed energy information of the corresponding light.

Although, in this embodiment, more than two rays of light received by the energy measuring device 614 are generated via the first beam splitter 104, it is not intended to limit the disclosure. In another embodiment, two or more light beams received by the energy measuring device 614 may also be formed by the light source 100. Therefore, the light passing through the first beam splitter 104 may be two or more. At this time, the energy measuring device 614 The number of sensing regions on the upper layer can also be divided into two or more, and the light from the first beam splitter 104 can be respectively corresponding to the light absorption energy information of the corresponding light.

Similarly, the portable mobile device 1100 of the eleventh embodiment can simultaneously perform optical rotation change and absorption energy variation between the light 110 emitted by the light source 102 and the light 110g, 100h transmitted to the photodetector group 606. Analysis, and the measurement of glucose information (eg, glucose value), because the glucose concentration in the eyeball (eg, aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, through this correspondence, and then read out with high accuracy Blood glucose information (eg, blood glucose levels). In addition, since the blood glucose monitoring function is integrated into the portable mobile device 1100, it is quite convenient in use. In addition, the mobile device can be connected to the cloud using a program or network of the portable mobile device 1100 to provide remote medical care.

FIG. 12 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to a twelfth embodiment of the present disclosure.

Referring to FIG. 7 and FIG. 12 simultaneously, the portable mobile device 1200 of the twelfth embodiment differs from the portable mobile device 700 of the seventh embodiment in that, in the portable mobile device 1200, the light 110 passes through the first After the two beamsplitter 404 reflects, two rays 110i, 110j are generated. In addition, the photodetector group 1206 of the portable mobile device 1200 includes a first photodetector 1208 and a second photodetector 1210, and the first photodetector 1208 and the second photodetector 1210 are located at the first The same side of the dichotomy 404. In this embodiment, the first photodetector 1208 and the second photodetector 1210 are, for example, located on a side of the second beam splitter 404 that reflects the light 110, and are respectively used to measure the light reflected by the second beam splitter 404. The light rays 110i, 110j produced by 110. One of the first photodetector 1208 and the second photodetector 1210 is, for example, an optical rotation measuring device for measuring optical rotation information, and the first photodetector 1208 and the second photodetector 1210 The other of them is, for example, an energy measuring device for measuring energy absorption information. In other embodiments, the first photodetector 1208 and the second photodetector 1210 can also include an optical rotation measuring device and an energy measuring device, respectively. The first photodetector 1208 and the second photodetector 1210 are coupled to the processing unit 108, for example, but are not intended to limit the disclosure. The components, connection relationships, and functions of the other components of the portable mobile device 1200 of the twelfth embodiment are similar to those of the portable mobile device 700 of the seventh embodiment, and the twelfth embodiment and the seventh embodiment The similar components are similar components, and the monitoring method of blood glucose can refer to the fourth embodiment, and thus will not be described herein.

In another embodiment, the first photodetector 1208 and the second photodetector 1210 may also be located on a side of the light 110 that penetrates the second beam splitter 404, and It is not used to measure the two rays 110a, 100b generated by the light 110 passing through the second beam splitter 404.

Similarly, the portable mobile device 1200 of the twelfth embodiment can simultaneously perform the optical change and the absorbed energy change between the light 110 emitted by the light source 102 and the light 110i, 110g transmitted to the photodetector group 1206. Analysis, and the measurement of glucose information (eg, glucose value), because the glucose concentration in the eyeball (eg, aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, through this correspondence, and then read out with high accuracy Blood glucose information (eg, blood glucose levels). In addition, since the blood glucose monitoring function is integrated into the portable mobile device 1200, it is quite convenient in use. In addition, the mobile device 800 can be connected to the cloud to provide remote medical care, and the blood glucose data can be used to remind or control the medication. In case of an emergency, the medical unit can be directly notified for medical care.

FIG. 13 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to a thirteenth embodiment of the present disclosure.

Referring to FIG. 12 and FIG. 13 simultaneously, the portable mobile device 1300 of the thirteenth embodiment is different from the portable mobile device 1200 of the twelfth embodiment in that the composition of the optical package 1304 of the thirteenth embodiment is The composition of the optical kit 1204 of the twelfth embodiment is different. The optical package 1304 is externally connected to the device body 602, and the optical package 1304 includes a first light splitter 104 and a lens group 608, and further includes a light source 102 and a second beam splitter 404, and more preferably includes a light information analyzing unit 116. And the warning device 118. The components, connection relationships, and functions of the other components of the portable mobile device 1300 of the thirteenth embodiment are the same as those of the twelfth embodiment. The components of the thirteenth embodiment are similar to those of the twelfth embodiment, and the components of the twelfth embodiment are similar to those of the twelfth embodiment.

Similarly, the portable mobile device 1300 of the thirteenth embodiment can simultaneously perform the optical change and the absorbed energy change between the light 110 emitted by the light source 102 and the light 110i, 110j transmitted to the photodetector group 606. Analysis, and the measurement of glucose information (eg, glucose value), because the glucose concentration in the eyeball (eg, aqueous humor in the eyeball) has a corresponding relationship with the blood glucose concentration, through this correspondence, and then read out with high accuracy Blood glucose information (eg, blood glucose levels). In addition, since the blood glucose monitoring function is integrated into the portable mobile device 1300, it is quite convenient in use. In addition, the mobile device can be connected to the cloud using a program or network of the portable mobile device 1300 to provide remote medical care.

In addition, although the non-invasive blood glucose monitoring device is applied to the portable mobile device as an example of the sixth embodiment to the thirteenth embodiment, it is not intended to limit the disclosure. A portable mobile device having non-invasive blood glucose monitoring function disclosed in the sixth embodiment to the thirteenth embodiment, which is capable of carrying out a non-invasive blood glucose monitoring function, can be carried out by a person skilled in the art. The concept of the device is combined with various embodiments of the first to fourth embodiments to develop a variety of portable mobile devices having non-invasive blood glucose monitoring functions.

In addition, although the first embodiment to the thirteenth embodiment are described by taking an eye as an example, it is not intended to limit the disclosure. Those skilled in the art can refer to the contents disclosed in the above embodiments. The present disclosure applies to embodiments of both eyes.

FIG. 14 is a schematic view showing a method for analyzing biochemical molecules according to a fourteenth embodiment of the present disclosure.

In this embodiment, the analysis method of the biochemical molecule is, for example, analyzed by a processing unit of the biochemical molecular monitoring device. The biochemical molecules to be analyzed are, for example, glucose, cholesterol, uric acid, water, lactic acid, urea, ascorbic acid or a combination thereof.

Referring to FIG. 14, step S202 can be performed to obtain an optical rotation change. The method of obtaining an optical rotation change includes the following steps. First, the portion of the plurality of optical rotation change values measured by the biochemical molecular monitoring device that exceeds the acceptable variation range is discarded. Next, the value of the optical rotation change is calculated using at least one mathematical statistical method. Among them, the mathematical statistical method is, for example, a least square error regression analysis method. The acceptable range of variation is, for example, a range expressed by the following mathematical formula.

Acceptable variation range of optical rotation change = arithmetic mean of optical rotation change value × (1 ± 15%)

Further, step S204 may be performed to obtain an absorption energy change. A method of obtaining a change in absorbed energy includes the following steps. First, the portion of the plurality of absorbed energy change values measured by the biochemical molecular monitoring device that exceeds the acceptable variation range is discarded. Next, the value of the absorbed energy change is calculated using at least one mathematical statistical method. Among them, the mathematical statistical method is, for example, a least square error regression analysis method. The acceptable range of variation is, for example, a range expressed by the following mathematical formula.

Acceptable range of variation in absorbed energy = value of absorbed energy change Arithmetic mean × (1 ± 15%)

Step S206 is performed to establish at least a first polynomial equation of the relationship between the biochemical molecule and the optical rotation change and at least a second polynomial equation of the relationship between the biochemical molecule and the absorbed energy. The biochemical molecule includes a target molecule and at least one interfering molecule, and the plurality of variables of the first polynomial equation and the second polynomial equation respectively include a target molecule concentration variable and an interference molecule concentration variable.

The first polynomial equation is established, for example, by a plurality of biochemical molecular concentration values stored in the database and corresponding plurality of optical rotation change values. The second polynomial equation is, for example, established by a plurality of biochemical molecular concentration values stored in the database and corresponding plurality of absorbed energy change values. The sample body of the plurality of biochemical molecular concentration values stored in the database includes a plurality of living samples or a plurality of standard samples.

In addition, the steps of establishing the first polynomial equation and the second polynomial equation further comprise distinguishing a plurality of optical rotation variation ranges from the plurality of absorption energy variation ranges, and having the first plurality of corresponding use in each of the optical rotation variation ranges The equation has a second polynomial equation that is used correspondingly in each range of absorbed energy variations.

For example, when the target molecule is glucose and the interfering molecule is lactic acid, and the range of three optical rotations and the range of three absorption energies are distinguished, the first polynomial equation and the second polynomial equation are selected as follows. Show, but this disclosure is not limited to this.

The first polynomial equation used in the first range of optical rotation: θ _{(glucose effect + lactic acid effect)} = a ₁ X _{glucose concentration} + b ₁ Y _{lactic acid concentration} + c ₁

The first polynomial equation used in the second range of optical rotation: θ _{(glucose effect + lactic acid effect)} = a ₁ 'X _{glucose concentration} + b ₁ 'Y _{lactic acid concentration} + c ₁ '

The first polynomial equation used in the third range of optical rotation: θ _{(glucose effect + lactic acid effect)} = a ₁ "X _{glucose concentration} + b ₁ "Y _{lactic acid concentration} + c ₁ "

Among them, θ _{(glucose effect + lactic acid influence)} is an optical rotation change, X _{glucose concentration} is a target molecular concentration variable, and Y _{lactic acid concentration} is an interference molecule concentration variable, a ₁ , a ₁ ', a ₁ ", b ₁ , b ₁ ', b ₁ ", c ₁ , c ₁ ' and c ₁ " are known coefficients.

The second polynomial equation is used in the range of the first absorbed energy variation: P _{(glucose effect + lactic acid influence)} = a ₂ X _{glucose concentration} + b ₂ Y _{lactic acid concentration} + c ₂

The second polynomial equation is used in the range of the second absorbed energy variation: P _{(glucose effect + lactic acid influence)} = a ₂ 'X _{glucose concentration} + b ₂ 'Y _{lactic acid concentration} + c ₂ '

The second polynomial equation is used in the range of the third absorbed energy variation: P _{(glucose effect + lactic acid influence)} = a ₂ "X _{glucose concentration} + b ₂ "Y _{lactic acid concentration} + c ₂ "

Among them, P _{(glucose effect + lactic acid effect)} is an optical rotation change, X _{glucose concentration} is a target molecular concentration variable, Y _{lactic acid concentration} is an interference molecule concentration variable, a ₂ , a ₂ ', a ₂ ", b ₂ , b ₂ ', b ₂ ", c ₂ , c ₂ ' and c ₂ " are known coefficients.

Going to step S208, the optical rotation change and the absorbed energy change measured by the biochemical molecular monitoring device are brought into the first polynomial equation and the second largest In the term equation, the first target molecule concentration of the target molecule when the target molecule and the interfering molecule are present simultaneously is calculated. The calculation method of the first target molecular concentration is, for example, solving the simultaneous equations of the first polynomial equation and the second polynomial equation. In the process of performing step S208, the change of the optical rotation and the change of the absorbed energy can be further analyzed by controlling the change factor to obtain the first target molecular concentration. The change factor includes a light emission frequency, a light energy intensity, a light on time length, a light off time length, a optomechanical space offset, or a combination thereof.

Further, steps S210, S212, S214, S216, S218, or a combination thereof are more selectively performed.

In step S210, at least a first graph or at least a third polynomial equation of the biochemical molecule relationship with the optical rotation change is established. Wherein, the variable of the third polynomial equation includes a target molecule concentration variable.

The first graph and the third polynomial equation are, for example, established by a plurality of biochemical molecular concentration values stored in the database and corresponding plurality of optical rotation change values. The sample body of the plurality of biochemical molecular concentration values stored in the database includes a plurality of living samples or a plurality of standard samples.

Further, the step of establishing the first graph or the third polynomial equation further includes distinguishing a plurality of optical rotation variation ranges, and having a corresponding first used pattern, a third polynomial equation, or a combination thereof in each of the optical rotation variation ranges.

For example, when the target molecule is glucose and three optical rotation ranges are distinguished, the third polynomial equation selected is as follows, but the disclosure is not limited thereto.

The third polynomial equation used in the first range of optical rotation: θ _{(glucose effect)} = a ₃ X _{glucose concentration} + c ₃

The third polynomial equation used in the second range of optical rotation: θ _{(glucose effect)} = a ₃ 'X _{glucose concentration} + c ₃ '

The third polynomial equation used in the third range of optical rotation: θ _{(glucose effect)} = a ₃ "X _{glucose concentration} + c ₃ "

Wherein θ _{(glucose effect)} is an optical rotation change, X _{glucose concentration} is a target molecular concentration variable, and a ₃ , a ₃ ', a ₃ ", c ₃ , c ₃ ' and c ₃ " are known coefficients.

In step S212, the optical rotation change measured by the biochemical molecular monitoring device is brought into the first chart, the third polynomial equation, or a combination thereof to calculate the second target molecular concentration of the target molecule. In the process of performing step S212, the optical rotation change can be analyzed by controlling the change factor to obtain the second target molecular concentration. The change factor includes a light emission frequency, a light energy intensity, a light on time length, a light off time length, a optomechanical space offset, or a combination thereof.

In step S214, at least a second chart or at least a fourth polynomial equation of the relationship between the biochemical molecule and the absorbed energy is established. Wherein, the variable of the fourth polynomial equation includes a target molecule concentration variable.

The second graph and the fourth polynomial equation are, for example, established by a plurality of biochemical molecular concentration values stored in the database and corresponding plurality of absorbed energy change values. The sample body of the plurality of biochemical molecular concentration values stored in the database includes a plurality of living samples or a plurality of standard samples.

Furthermore, the step of establishing the second graph or the fourth polynomial equation further comprises distinguishing a plurality of ranges of absorbed energy variations, and having a second graph, a fourth polynomial equation or a correspondingly used equation for each absorbed energy variation range or combination.

For example, when the target molecule is glucose and the three ranges of absorbed energy are distinguished, the fourth polynomial equation selected is as follows, but the disclosure is not limited thereto.

The fourth polynomial equation used in the first range of absorbed energy variations: P _{(glucose effect)} = a ₄ X _{glucose concentration} + c ₄

The fourth polynomial equation used in the second range of absorbed energy variations: P _{(glucose effect)} = a ₄ 'X _{glucose concentration} + c ₄ '

The fourth polynomial equation used in the third range of absorbed energy variations: P _{(glucose effect)} = a ₄ "X _{glucose concentration} + c ₄ "

Among them, P _{(glucose effect)} is a change in absorbed energy, X _{glucose concentration} is a target molecular concentration variable, and a ₄ , a ₄ ', a ₄ ", c ₄ , c ₄ ' and c ₄ " are known coefficients.

In step S216, the change in absorbed energy measured by the biochemical molecular monitoring device is brought into a second chart, a fourth polynomial equation, or a combination thereof to calculate a third target molecular concentration of the target molecule. In the process of performing step S216, the absorption energy change can be analyzed by controlling the change factor to obtain the third target molecule concentration. Wherein, the change factor includes a light emission frequency, a light energy intensity, a light on time length, a light off time length, Optomechanical component space offset or a combination thereof.

In step S218, the final target molecular concentration is determined from the first target molecular concentration, the second target molecular concentration, the third target molecular concentration, or a combination thereof. In other embodiments, when step S218 is not performed, the first target molecular concentration obtained in step S208 can be taken as the final target molecular concentration.

As can be seen from the above-described fourteenth embodiment, the above-described biochemical molecular analysis method can obtain a target molecule concentration when both the target molecule and the interfering molecule are present by the change in the optical rotation and the absorption energy, and thus a more accurate target molecule concentration can be obtained.

In summary, the above embodiment has at least the following features:

1. The non-invasive blood glucose monitoring device proposed by the above embodiment can accurately measure the glucose information (eg, glucose value) of the measurement object due to glucose in the eyeball (eg, aqueous humor in the eyeball). The concentration has a corresponding relationship with the blood glucose concentration, and the blood glucose information (for example, blood sugar level) is read through the correspondence.

2. The non-invasive blood glucose monitoring device proposed in the above embodiment can be used for miniaturization, thereby improving the convenience of use.

3. The portable mobile device having the non-invasive blood glucose monitoring function proposed in the above embodiment is not particularly limited in use, and can be used indoors or outdoors.

4. The blood glucose level of the measurement subject can be continuously and instantaneously obtained by the non-invasive blood glucose monitoring method proposed in the above embodiment.

5. The method for analyzing biochemical molecules proposed in the above embodiments can be rotated by The light change and the absorption energy change, and the target molecule concentration when the target molecule and the interference molecule are present simultaneously are obtained, so that a more accurate target molecule concentration can be obtained.

The present disclosure has been disclosed in the above preferred embodiments. However, it is not intended to limit the scope of the disclosure, and the invention may be modified and modified without departing from the spirit and scope of the disclosure. The scope of protection is subject to the definition of the scope of the patent application.

100, 300, 400, 500‧‧‧ non-invasive blood glucose monitoring device

102‧‧‧Light source

104‧‧‧First beam splitter

106, 306, 406, 506, 606, 1206‧‧‧Photodetector group

108‧‧‧Processing unit

110, 110a, 100b, 110c, 110d, 110e, 110f, 110g, 110h, 110i, 110j‧‧‧ rays

112, 312, 412, 416, 612, 616‧‧‧ optical rotation measuring device

112a‧‧‧Polarizer

112b‧‧‧Photosensitive element

113, 115‧‧ ‧ light barrier

113a, 115a‧‧ hole

114, 314, 414, 418, 614, 618‧‧‧ energy measuring devices

116‧‧‧Light Information Analysis Unit

118‧‧‧ warning device

120‧‧‧ Eye sighting positioning device

122‧‧ Sight

124‧‧‧Connecting components

126‧‧‧ sheath

200‧‧‧ eyeballs

202‧‧‧ front room

204‧‧‧ aqueous liquid

404‧‧‧Second splitter

408, 508, 1208‧‧‧ first photodetector

410, 510, 1210‧‧‧ second photodetector

600, 700, 800, 900, 1000, 1100, 1200‧‧‧ portable mobile devices

601‧‧‧ light exit

602‧‧‧ device body

604, 904, 1004, 1204, 1304‧‧‧ optical kit

608‧‧‧ lens group

614a, 614b, 614c, 614d‧‧‧ Sensing area

1006‧‧‧ lens

S90, S100, S102, S104, S106, S108, S110, S112, S114, S116, S202, S204, S206, S208, S210, S212, S214, S216, S218‧‧

FIG. 1A is a schematic diagram of a non-invasive blood glucose monitoring device according to a first embodiment of the present disclosure.

FIG. 1B is a schematic diagram of the optical rotation measuring device of FIG. 1A.

2 is a schematic diagram of a non-invasive blood glucose monitoring device according to a second embodiment of the present disclosure.

FIG. 3 is a schematic diagram of a non-invasive blood glucose monitoring device according to a third embodiment of the present disclosure.

FIG. 4 is a schematic diagram of a non-invasive blood glucose monitoring device according to a fourth embodiment of the present disclosure.

FIG. 5 is a flow chart showing a non-invasive blood glucose monitoring method according to a fifth embodiment of the present disclosure.

FIG. 6 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to a sixth embodiment of the present disclosure.

FIG. 7 illustrates a non-invasive blood of a seventh embodiment of the present disclosure. Schematic diagram of a portable mobile device for sugar monitoring functions.

FIG. 8 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to an eighth embodiment of the present disclosure.

FIG. 9 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to a ninth embodiment of the present disclosure.

FIG. 10 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to a tenth embodiment of the present disclosure.

FIG. 11 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to an eleventh embodiment of the present disclosure.

FIG. 12 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to a twelfth embodiment of the present disclosure.

FIG. 13 is a schematic diagram of a portable mobile device having a non-invasive blood glucose monitoring function according to a thirteenth embodiment of the present disclosure.

FIG. 14 is a schematic view showing a method for analyzing biochemical molecules according to a fourteenth embodiment of the present disclosure.

100‧‧‧ Non-invasive blood glucose monitoring device

102‧‧‧Light source

104‧‧‧First beam splitter

106‧‧‧Photodetector group

108‧‧‧Processing unit

110‧‧‧Light

112‧‧‧Aperture measuring device

115‧‧‧Light barrier

115a‧‧ hole

114‧‧‧ Energy measuring device

116‧‧‧Light Information Analysis Unit

118‧‧‧ warning device

120‧‧‧ Eye sighting positioning device

122‧‧ Sight

124‧‧‧Connecting components

126‧‧‧ sheath

200‧‧‧ eyeballs

202‧‧‧ front room

204‧‧‧ aqueous liquid

Claims (126)

A non-invasive blood glucose monitoring device comprising: at least one light source emitting at least one light; a first optical splitter having a focusing function for causing the light emitted by the light source to be incident and focused by the first optical splitter Going into a ball; a photodetector group measuring an optical rotation information and an absorption energy information of the light reflected by the eyeball and transmitted to the photodetector group by the first beam splitter; a processing unit that receives and processes the optical rotation information and the absorbed energy information to obtain an optical rotation change and an absorption energy change between the light emitted by the light source and the light transmitted to the photodetector group, Obtaining a biochemical molecular information of a biochemical molecule, the biochemical molecule includes at least one glucose, and the processing unit obtains a glucose information by using the biochemical molecular information, and the glucose information has a correspondence relationship with the blood glucose information, thereby reading The blood sugar information. The non-invasive blood glucose monitoring device of claim 1, wherein a wavelength of the light source comprises a glucose absorbable wavelength. The non-invasive blood glucose monitoring device of claim 1, wherein a wavelength of the light source comprises a wavelength in the infrared light. The non-invasive blood glucose monitoring device of claim 1, wherein the light source comprises a light emitting diode or a laser diode. The non-invasive blood glucose monitoring device of claim 1, wherein the light comprises a linearly polarized light, a circularly polarized light, an elliptically polarized light or a partially polarized light. The non-invasive blood glucose monitoring device according to claim 1, wherein the light source has a function of controlling a transmitting frequency of the light, a function of controlling an intensity of the light, and a function of controlling an opening time of the light. a function that controls the length of time of the light to be turned off or a combination thereof. The non-invasive blood glucose monitoring device according to claim 1, further comprising an optical information analyzing unit that detects a light information of the light from the first beam splitter before the light is incident on the eyeball And transmitting the optical information to the processing unit, a warning device or a light source control unit to perform feedback control on an optical characteristic of the light. The non-invasive blood glucose monitoring device of claim 7, wherein the optical information analyzing unit comprises at least one of an optical power meter and a light sensor, the light detected by the optical power meter The information is an energy information, and the light information detected by the light sensor is at least one of the energy information and a location information. The non-invasive blood glucose monitoring device according to claim 1, wherein the first beam splitter focuses the light to an anterior chamber of the eyeball, and the light reflected by the eyeball includes water from a room The reflected light of the liquid. The non-invasive blood glucose monitoring device of claim 1, wherein the first beam splitter comprises an optical film, a lens, a grating, a diffractive optical element or a combination of any of the above. The non-invasive blood glucose monitoring device according to claim 1, wherein the photodetector group includes an optical rotation measuring device and an energy measuring device, respectively measuring the reflection by the eyeball, and then First beam splitter The light that reflects or passes through the first beam splitter. The non-invasive blood glucose monitoring device of claim 11, wherein the optical rotation measuring device comprises an active optical rotation measuring device or at least one passive optical rotation measuring device. The non-invasive blood glucose monitoring device according to claim 12, wherein the active optical rotation measuring device comprises an analyzer, and the analyzer directly calculates the optical rotation information. The non-invasive blood glucose monitoring device according to claim 12, wherein the passive optical rotation measuring device comprises a polarizing plate, and the passive optical measuring device measures the energy of the light passing through the polarizing plate. Calculate the optical information. The non-invasive blood glucose monitoring device according to claim 11, wherein the energy measuring device and the optical rotation measuring device respectively comprise a photosensitive element. The non-invasive blood glucose monitoring device of claim 15, wherein the photosensitive element comprises a charge coupled device, a complementary metal oxide semiconductor sensor or a photodiode. The non-invasive blood glucose monitoring device according to claim 15, further comprising a light blocking plate having a hole, the light is first passed through the hole of the light blocking plate and then transmitted to the photosensitive element. The non-invasive blood glucose monitoring device of claim 17, wherein the light barrier comprises a metal mask or a quartz glass mask. The non-invasive blood glucose monitoring device according to claim 1, wherein the biochemical molecule comprises a cholesterol, a uric acid, a water, and a Lactic acid, monourea, ascorbic acid or a combination thereof. The non-invasive blood glucose monitoring device of claim 1, wherein the biochemical molecule comprises an interfering molecule. The non-invasive blood glucose monitoring device according to claim 20, wherein in the process of obtaining the glucose information by the processing unit, the processing unit excludes interference caused by the interference molecule. The non-invasive blood glucose monitoring device of claim 1, wherein the processing unit comprises an analog digital integrated circuit module, wherein the analog digital integrated circuit module comprises a microprocessor, an amplifier and an analog digital converter. The non-invasive blood glucose monitoring device of claim 22, wherein the analog digital integrated circuit module further comprises a wireless transmission device. The non-invasive blood glucose monitoring device of claim 1, wherein the processing unit analyzes the optical rotation information and the absorbed energy information by controlling a light source change, a light machine component spatial offset or a combination thereof. The glucose information includes a change in light emission frequency, a change in light energy intensity, a change in length of a light on time, or a change in length of a light off time, or a combination thereof. The non-invasive blood glucose monitoring device according to claim 1, further comprising a second beam splitter, wherein the light reflected by the eyeball and transmitted by the first beam splitter is transmitted to the light detector group. The non-invasive blood glucose monitoring device of claim 25, wherein the photodetector group comprises a first photodetector and a second light a detector for measuring the light reflected by the second beam splitter or passing through the second beam splitter. The non-invasive blood glucose monitoring device of claim 26, wherein the first photodetector and the second photodetector respectively comprise an optical rotation measuring device and an energy measuring device. The non-invasive blood glucose monitoring device of claim 26, wherein one of the first photodetector and the second photodetector is an optical rotation measuring device, the first optical detecting The other of the second photodetector and the second photodetector is an energy measuring device. The non-invasive blood glucose monitoring device of claim 25, wherein the second beam splitter comprises an optical film, a lens, a grating, a diffractive optical element or a combination of any of the above. The non-invasive blood glucose monitoring device according to claim 1, further comprising an eye aiming positioning device for aligning an eye's line of sight with the eye aiming positioning device to determine the eyeball. Measuring position. The non-invasive blood glucose monitoring device of claim 30, wherein the eye targeting device comprises a light spot, a logo or an embossed pattern. The non-invasive blood glucose monitoring device according to claim 1, further comprising a connecting component, one end of the connecting component is connected to an optical outlet of the non-invasive blood glucose monitoring device, and the other end of the connecting component is used for attaching Rely on the outer edge of an eye. Non-invasive blood glucose monitoring as described in Section 32 of the patent application The device further includes a sheath disposed on the side of the connecting member for abutting against the outer edge of the eye. The non-invasive blood glucose monitoring device of claim 33, wherein the sheath comprises a disposable sheath. A portable mobile device having a non-invasive blood glucose monitoring function, comprising: a device body; at least one light source emitting at least one light; an optical package mounted on the device body and including a first beam splitter Wherein, the first beam splitter has a focusing function, so that the light emitted by the light source is incident by the first beam splitter and is focused into an eyeball; a photodetector group, the measurement is reflected by the eyeball And an optical rotation information and an absorption energy information of the light transmitted by the first optical splitter to the photodetector group; and a processing unit disposed in the apparatus body and receiving and processing the optical rotation information and Absorbing energy information to obtain an optical rotation change and an absorption energy change between the light emitted by the light source and the light transmitted to the photodetector group to obtain a biochemical molecular information of a biochemical molecule, The biochemical molecule includes at least one glucose, and the processing unit obtains a glucose information by using the biochemical molecular information, and the glucose information has a correspondence with the blood glucose information. And then read the glucose information. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, wherein the light source is disposed in the device body. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, wherein the light source is part of the optical kit. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, wherein a wavelength of the light source comprises a glucose absorbable wavelength. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, wherein a wavelength of the light source comprises a wavelength in an infrared light. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, wherein the light source comprises a light emitting diode or a laser diode. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, wherein the light comprises a linearly polarized light, a circularly polarized light, an elliptically polarized light or a partially polarized light. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, wherein the light source has a function of controlling a transmission frequency of the light, a function of controlling an intensity of the light, and controlling the light. A function that turns on the length of time, a function that controls the length of a closed time, or a combination thereof. The portable mobile device with non-invasive blood glucose monitoring function according to claim 35, further comprising an optical information analyzing unit, detecting the first optical splitter before the light is incident on the eyeball a light information of the light, and transmitting the light information to the processing unit, A warning device or a light source control unit for feedback control of an optical characteristic of the light. The portable mobile device with non-invasive blood glucose monitoring function according to claim 43 , wherein the optical information analyzing unit comprises at least one of an optical power meter and a light sensor, the optical power The light information detected by the meter is an energy information, and the light information detected by the light sensor is at least one of the energy information and a position information. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 44, wherein at least one of the optical power meter and the optical sensor is disposed in the device body. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 44, wherein at least one of the optical power meter and the optical sensor is part of the optical kit. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, wherein the first optical splitter focuses the light to an anterior chamber of the eyeball, and the light is reflected by the eyeball The light includes reflected light from a room of water. The portable mobile device having the non-invasive blood glucose monitoring function according to claim 35, wherein the first optical splitter comprises an optical film, a lens, a grating, a diffractive optical element or any of the above A combination of components. The portable mobile device with non-invasive blood glucose monitoring function according to claim 35, wherein the photodetector group comprises an optical rotation measuring device and an energy measuring device, respectively measuring the eyeball Counter And illuminating the light transmitted by the first beam splitter. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 49, wherein the energy measuring device is disposed in the device body. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 49, wherein the optical rotation measuring device is disposed in the device body. A portable mobile device having a non-invasive blood glucose monitoring function as described in claim 49, wherein the optical rotation measuring device is part of the optical package. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 49, wherein the optical rotation measuring device comprises an active optical rotation measuring device or at least one passive optical rotation measuring device. The portable mobile device with non-invasive blood glucose monitoring function according to claim 53, wherein the active optical rotation measuring device comprises an analyzer, and the optical device directly calculates the optical rotation information. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 53 wherein the passive optical rotation measuring device comprises a polarizing plate, and the passive optical measuring device passes the polarization through the measurement. The optical information of the piece of light is used to calculate the optical information. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 49, wherein the energy measuring device and the optical rotation measuring device respectively comprise a photosensitive element. Non-invasive blood glucose as described in claim 56 A portable mobile device for monitoring functions, wherein the photosensitive element comprises a charge coupled device, a complementary metal oxide semiconductor sensor or a photodiode. The portable mobile device with non-invasive blood glucose monitoring function according to claim 56, further comprising a light blocking plate having a hole, the light is first passed through the hole of the light blocking plate, and then the light is first passed through the hole of the light blocking plate. Transfer to the photosensitive element. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 58 wherein the light barrier comprises a metal mask or a quartz glass mask. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, wherein the biochemical molecule comprises a cholesterol, a uric acid, a monohydrate, a lactic acid, a urea, an ascorbic acid or a combination thereof. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, wherein the biochemical molecule comprises an interference molecule. The portable mobile device with non-invasive blood glucose monitoring function according to claim 61, wherein the processing unit interferes with the interfering molecule in the process of obtaining the glucose information by the processing unit Exclude. The portable mobile device with non-invasive blood glucose monitoring function according to claim 35, wherein the processing unit comprises an analog digital integrated circuit module, wherein the analog digital integrated circuit module comprises a microprocessor An amplifier and an analog-to-digital converter. The portable mobile device with non-invasive blood glucose monitoring function according to claim 63, wherein the analog digital integrated circuit module further comprises a wireless transmission device. The portable mobile device with non-invasive blood glucose monitoring function according to claim 35, wherein the processing unit analyzes the optical rotation information by controlling a light source change, a light machine component spatial offset or a combination thereof. The energy information is acquired to obtain the glucose information, and the light source change includes a change in light emission frequency, a change in light energy intensity, a change in length of a light on time, a change in length of a light off time, or a combination thereof. The portable mobile device with non-invasive blood glucose monitoring function according to claim 35, further comprising a second beam splitter, the light reflected by the eyeball and transmitted by the first beam splitter Transfer to the photodetector group. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 66, wherein the second optical splitter is disposed in the device body. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 66, wherein the second optical splitter is part of the optical package. The portable mobile device with non-invasive blood glucose monitoring function according to claim 66, wherein the photodetector group comprises a first optical measuring device, a first energy measuring device, and a first a second optical measuring device and a second energy measuring device are disposed in the device body, wherein the first optical measuring device and the first energy measuring device respectively measure The light reflected by the eyeball and transmitted by the first beam splitter, and the second optical measuring device and the second energy measuring device are respectively configured to measure the light transmitted by the second beam splitter . A portable mobile device having a non-invasive blood glucose monitoring function according to claim 66, wherein the photodetector group includes a first photodetector and a second photodetector, respectively The light reflected by the second beam splitter or passing through the second beam splitter is measured. The portable mobile device with non-invasive blood glucose monitoring function according to claim 70, wherein the first photodetector and the second photodetector respectively comprise an optical rotation measuring device and an energy Measuring device. The portable mobile device with non-invasive blood glucose monitoring function according to claim 70, wherein one of the first photodetector and the second photodetector is an optical rotation measuring device The other of the first photodetector and the second photodetector is an energy measuring device. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 66, wherein the second optical splitter comprises an optical film, a lens, a grating, a diffractive optical element or any of the above A combination of components. The portable mobile device having the non-invasive blood glucose monitoring function according to claim 35, wherein the photodetector group includes a plurality of optical rotation measuring devices when the first optical splitter transmits a plurality of light rays. And an energy measuring device, wherein the optical rotation measuring devices and the plurality of sensing regions of the energy measuring device are respectively used to measure the corresponding light rays. Non-invasive blood glucose as described in claim 35 A portable mobile device that monitors functionality, wherein the optical package further includes a lens set. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 75, wherein when the optical kit has the lens set, the optical package is integrated as a lens in a camera module. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 35, further comprising an eye aiming positioning device for aligning an eye's line of sight with the eye aiming positioning device Alignment to determine the measurement position of the eye. A portable mobile device having a non-invasive blood glucose monitoring function according to claim 77, wherein the eye aiming positioning device comprises a light spot, a logo or an embossed pattern. The portable mobile device with non-invasive blood glucose monitoring function according to claim 35, further comprising a connecting component, one end of the connecting component being connected to the portable action with non-invasive blood glucose monitoring function A light exit of the device, the other end of the connecting element is used to abut the outer edge of an eye. The portable mobile device with non-invasive blood glucose monitoring function according to claim 79, further comprising a sheath disposed on the side of the connecting member for abutting against the outer edge of the eye. A portable mobile device having a non-invasive blood glucose monitoring function as described in claim 80, the sheath comprising a disposable sheath. A non-invasive blood glucose monitoring method includes: emitting at least one light by at least one light source; The light emitted by the light source is incident by a first beam splitter having a focusing function and is focused into an eyeball; the light reflected by the eyeball is transmitted to a light detecting by the first beam splitter The optical detector group measures an optical rotation information and an absorption energy information of the light transmitted to the photodetector group; and obtains the optical light by processing the optical rotation information and the absorbed energy information An optical rotation change and an absorption energy change between the emitted light and the light transmitted to the photodetector group; and the optical rotation change and the absorption energy change are analyzed to obtain a biochemical molecule biochemical According to the molecular information, the biochemical molecule includes at least one glucose, and the glucose information is obtained by the biochemical molecular information. Since the glucose information has a correspondence with the blood glucose information, the blood glucose information is read through the correspondence. The non-invasive blood glucose monitoring method according to claim 82, wherein the means for obtaining and analyzing the optical rotation change and the absorbed energy change comprises a processing unit. The non-invasive blood glucose monitoring method according to claim 83, wherein the processing unit comprises an analog digital circuit integration module, wherein the analog digital integration module comprises a microprocessor, an amplifier and an analog digital converter. The non-invasive blood glucose monitoring method according to claim 84, wherein the analog digital circuit integration module further comprises a wireless transmission device. The method of non-invasive blood glucose monitoring according to claim 82, further comprising controlling an optical characteristic of the light source, a spatial displacement of the optical component, or a combination thereof, wherein the optical characteristic comprises controlling the light by the light source A firing frequency, an intensity of the light, an opening time length, a closing time length of the light, or a combination thereof. The non-invasive blood glucose monitoring method of claim 82, further comprising: detecting a light information of the light from the first beam splitter before the light is incident on the eyeball, to An optical characteristic performs a feedback control. The non-invasive blood glucose monitoring device of claim 87, wherein the light information comprises at least one of energy information and a location information. The non-invasive blood glucose monitoring method of claim 87, wherein the means for detecting the optical information comprises at least one of an optical power meter and a light sensor. The non-invasive blood glucose monitoring method according to claim 87, wherein the device for performing the feedback control on the optical characteristic comprises a processing unit, a warning device or a light source control unit. The non-invasive blood glucose monitoring method according to claim 82, wherein the biochemical molecule comprises a cholesterol, a uric acid, a monohydrate, a lactic acid, a urea, an ascorbic acid or a combination thereof. The non-invasive blood glucose monitoring method according to claim 82, wherein the biochemical molecule comprises an interference molecule. Non-invasive blood glucose monitoring as described in Section 92 of the patent application The method wherein the step of obtaining the glucose information further comprises eliminating interference caused by the interfering molecule. The non-invasive blood glucose monitoring method according to claim 82, wherein the first beam splitter focuses the light to an anterior chamber of the eyeball, and the light reflected by the eyeball includes water from a room The reflected light of the liquid. The non-invasive blood glucose monitoring method according to claim 82, wherein the photodetector group comprises an optical rotation measuring device and an energy measuring device for respectively measuring the light reflected by the eyeball. The method of non-invasive blood glucose monitoring according to claim 82, further comprising transmitting the light reflected by the eyeball to the second beam splitter by the first beam splitter, and then using the second beam splitter Transfer to the photodetector group. The non-invasive blood glucose monitoring method of claim 96, wherein the photodetector group includes a first photodetector and a second photodetector, respectively for measuring the second The light reflected by or passing through the second beam splitter. The non-invasive blood glucose monitoring method of claim 97, wherein the first photodetector and the second photodetector comprise an optical rotation measuring device and an energy measuring device. The non-invasive blood glucose monitoring method of claim 97, wherein one of the first photodetector and the second photodetector is an optical rotation measuring device, the first optical detecting The other of the second photodetector and the second photodetector is an energy measuring device. The non-invasive blood glucose monitoring method according to claim 82, wherein the method for measuring the optical rotation of the photodetector group comprises an active optical rotation angle measurement method and a passive optical rotation angle measurement method. The non-invasive blood glucose monitoring method according to claim 100, wherein the active optical rotation angle measurement method comprises directly calculating the optical rotation information by using an analyzer. The non-invasive blood glucose monitoring method according to claim 100, wherein the passive optical rotation angle measuring method comprises measuring the optical rotation information by at least one passive optical rotation measuring device, and the passive optical rotation measuring device comprises a A polarizing plate, the passive optical measuring device measures the energy of the light passing through the polarizing plate to calculate the optical rotation information. The non-invasive blood glucose monitoring method according to claim 82, further comprising aiming the eyeball at an eye aiming positioning device for aligning the line of sight of an eye with the positioning device for eye sighting, To determine the measurement position of the eyeball. A method for analyzing biochemical molecules, comprising: establishing at least a first polynomial equation relating a biochemical molecule to an optical rotation change, and at least a second polynomial equation of the biochemical molecule and an absorption energy change, wherein the biochemical The molecule includes a target molecule and at least one interfering molecule, and the plurality of variables of the first polynomial equation and the second polynomial equation respectively include a target molecular concentration variable and an interfering molecule concentration variable; and The optical rotation change measured by the biochemical molecular monitoring device and the absorption energy change are brought into the first polynomial equation and the second polynomial In the equation, a first target molecule concentration of the target molecule when the target molecule and the interfering molecule are simultaneously present is calculated. The method for analyzing a biochemical molecule according to claim 104, wherein the calculating method of the first target molecular concentration comprises solving the simultaneous equation of the first polynomial equation and the second polynomial equation. The method for analyzing biochemical molecules according to claim 104, wherein the first polynomial equation is established by a plurality of biochemical molecular concentration values stored in a database and corresponding plurality of optical rotation change values. The second polynomial equation is established by the values of the plurality of biochemical molecules stored in the database and the corresponding values of the plurality of absorbed energy changes. The method for analyzing biochemical molecules according to claim 106, wherein the sample body of the plurality of biochemical molecule concentration values stored in the database comprises a plurality of living samples or a plurality of standard samples. The method for analyzing a biochemical molecule according to claim 104, wherein the method for obtaining the optical rotation change comprises: a portion of the plurality of optical rotation change values measured by the biochemical molecular monitoring device exceeding an acceptable variation range Round off; and use at least one mathematical statistical method to calculate the value of the optical rotation change. The method for analyzing biochemical molecules according to claim 108, wherein the mathematical statistical method comprises a least square error regression analysis method. Analysis of biochemical molecules as described in Section 108 of the patent application The method wherein the acceptable range of variation comprises an arithmetic mean of the value of the optical rotation change x (1 ± 15%). The method for analyzing a biochemical molecule according to claim 104, wherein the method for obtaining the change in the absorbed energy comprises: the plurality of absorbed energy change values measured by the biochemical molecular monitoring device exceeds an acceptable variation range Partially rounded off; and using at least one mathematical statistical method to calculate the value of the absorbed energy change. The method for analyzing biochemical molecules according to claim 111, wherein the mathematical statistical method comprises a least square error regression analysis method. The method for analyzing biochemical molecules according to claim 111, wherein the acceptable variation range comprises an arithmetic mean of the value of the absorbed energy change × (1 ± 15%). The method for analyzing biochemical molecules according to claim 104, wherein the step of establishing the first polynomial equation and the second polynomial equation further comprises: distinguishing a plurality of optical rotation ranges from the plurality of absorption energies The range of variation, and having the first polynomial equation used correspondingly in each of the optical rotation variation ranges, has the second polynomial equation correspondingly used in each of the absorption energy variation ranges. For the analysis method of the biochemical molecule described in claim 104, the step of calculating the concentration of the first target molecule further comprises: analyzing the optical rotation change and the absorbed energy by controlling a change factor. Varying to obtain the first target molecule concentration, the change factor comprising a light emission frequency, a light energy intensity, a light on time length, a turn off time length, a optomechanical space offset, or a combination thereof. The method for analyzing a biochemical molecule according to claim 104, further comprising: establishing at least a first graph or at least a third polynomial equation of the biochemical molecule and the optical rotation change, wherein the third plurality The variable of the equation includes the target molecule concentration variable; the optical rotation change measured by the biochemical molecular monitoring device is brought into the first chart, the third polynomial equation or a combination thereof to calculate the target molecule a second target molecule concentration; and determining a final target molecule concentration from the first target molecule concentration and the second target molecule concentration. The method for analyzing biochemical molecules according to claim 116, wherein the first graph and the third polynomial equation are a plurality of corresponding biochemical molecular concentration values stored in a database. The value of the optical rotation change is established. The method for analyzing biochemical molecules according to claim 116, wherein the step of establishing the first graph or the third polynomial equation further comprises: distinguishing a plurality of optical rotation ranges, and each of the optical rotation ranges The first graph, the third polynomial equation, or a combination thereof used accordingly. Analysis of biochemical molecules as described in claim 116 The method further includes: establishing at least a second graph or at least a fourth polynomial equation of the biochemical molecule in relation to the change in absorbed energy, wherein the variable of the fourth polynomial equation includes the target molecule concentration variable; The absorbed energy change measured by the biochemical molecular monitoring device is brought into the second graph, the fourth polynomial equation or a combination thereof to calculate a third target molecular concentration of the target molecule; and by the first The target molecule concentration, the second target molecule concentration, the third target molecule concentration, or a combination thereof determines the final target molecule concentration. The method for analyzing biochemical molecules according to claim 119, wherein the second graph and the fourth polynomial equation are a plurality of corresponding biochemical molecular concentration values stored in a database. The value of the absorbed energy change is established. The method for analyzing biochemical molecules according to claim 119, wherein the step of establishing the second chart or the fourth polynomial equation further comprises: distinguishing a plurality of absorption energy variation ranges, and each of the absorbed energy The range of variation has the second graph, the fourth polynomial equation, or a combination thereof used accordingly. The method for analyzing a biochemical molecule according to claim 104, further comprising: establishing at least a second graph or at least a fourth polynomial equation of the biochemical molecule in relation to the change in absorbed energy, wherein the fourth plurality The variable of the term equation includes the target molecule concentration variable; The absorption energy change measured by the biochemical molecular monitoring device is brought into the second chart, the fourth polynomial equation or a combination thereof to calculate a third target molecular concentration of the target molecule; A target molecule concentration and the third target molecule concentration determine a final target molecule concentration. The method for analyzing biochemical molecules according to claim 122, wherein the second graph and the fourth polynomial equation are a plurality of corresponding biochemical molecular concentration values stored in a database. The value of the absorbed energy change is established. The method for analyzing biochemical molecules according to claim 122, wherein the step of establishing the second graph or the fourth polynomial equation further comprises: distinguishing a plurality of absorption energy variation ranges, and each of the absorption energies The range of variation has the second graph, the fourth polynomial equation, or a combination thereof used accordingly. The method for analyzing a biochemical molecule according to claim 104, wherein the biochemical molecule comprises a glucose, a cholesterol, a uric acid, a monohydrate, a lactic acid, a urea, an ascorbic acid or a combination thereof. The method for analyzing biochemical molecules according to claim 104, wherein the analysis method is performed by a processing unit of the biochemical molecular monitoring device.