KR101661287B1 - Method For Non-Invasive Glucose Measurement And Non-Invasive Glucose Measuring Apparatus using the same Method - Google Patents

Abstract

The present invention provides a bloodless blood glucose measurement method and a bloodless blood glucose measurement apparatus. The present invention provides a bloodless blood glucose measurement method and a bloodless blood glucose measurement device capable of measuring a blood glucose amount more accurately by reflecting pulsation of a blood vessel serving as a factor of error in measurement of blood glucose amount in blood glucose measurement by bloodless blood collection do.

Description

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a non-blood-containing glucose measurement device and a non-blood-containing glucose measurement device using the non-

The present invention relates to a bloodless blood glucose measuring apparatus, and more particularly, to a bloodless blood glucose measuring apparatus and a bloodless blood glucose measuring method for improving the accuracy of bloodless blood glucose prediction by reflecting pulsation of a blood vessel.

Diabetes is one of the most common diseases of modern people. Even in the US alone, more than 5% of the total population is suffering from diabetes.

Diabetes is a hormone secreted by the pancreas is less secreted or not function properly, the sugar in the blood is transferred to the cells can not be used as energy and blood sugar accumulation in the blood, hypertension, kidney failure, vision damage can cause complications have.

Diet, exercise and drug therapy are being performed to manage the sugar in the blood. Knowing the exact amount of blood sugar on the basis of these therapies is basic.

Conventional devices for analyzing the concentration of a blood component of a patient are known. These devices utilize a small sample of blood taken from a finger tip, which samples a blood sample into a chemically treated sensor and inserts it into a portable device to measure the concentration of the blood component.

The method of measuring the concentration of the blood component by stabbing the finger with blood is problematic in that it is painful and causes various problems when it should be frequently performed. In other words, the price of the device is not expensive, but is exposed to maintenance costs of disposable items for blood collection, open bleeding, and health risks associated with infection. In addition, the time difference between the time of placing the blood sample in the chemically treated carrier and the time of inserting the carrier into the instrument is inaccurate in measuring the concentration of the blood component. Thus, there is a widespread demand for an apparatus for the measurement of blood glucose concentration of millions of diabetic patients.

The blood glucose measurement method most commonly used up to now is an electrochemical detection method using an enzyme called glucose oxidase (glucose oxidase). The blood stuck to the finger tip of the finger is put on an electrode having a pattern of glucose oxidase, The reduction potential is applied to measure the amount of current depending on the amount of glucose.

On the other hand, the bloodless blood glucose measuring apparatus has a problem that the accuracy of blood glucose measurement is not high.

The present invention provides a bloodless blood glucose measurement device capable of correcting an error of blood glucose measurement according to a difference between a maximum diastolic blood pressure and a maximum systolic blood pressure.

An apparatus for measuring bloodless blood glucose according to an aspect of the present invention includes: a measurement unit for measuring a Raman scattering signal of a target object; And a controller for acquiring the intensity of the measured Raman scattering signal and acquiring a correction factor based on a change in a maximum diastolic and a systolic blood vessel state of the blood vessel included in the subject.

According to another aspect of the present invention, there is provided an apparatus for measuring bloodless blood glucose comprising: a measuring unit for measuring a maximum diastolic and a systolic blood vessel state of a blood vessel included in a subject; And a controller for acquiring a correction factor based on the measured change in the blood vessel state and acquiring a blood glucose level based on the correction factor.

According to an aspect of the present invention, there is provided a bloodless blood glucose measuring method comprising: measuring a Raman scattering signal of a subject; Obtaining an intensity of the measured Raman scattering signal; Obtaining a correction factor based on changes in a maximum diastolic and a systolic blood vessel state of the subject included in the subject; Comparing the reference factor and the correction factor when acquiring the relation function; And acquiring a blood glucose level using the relational function based on the result of the comparison step and the intensity of the Raman scattering signal, wherein the relation function is a relationship between the intensity of the scatter signal And the reference parameter is obtained on the basis of a change in the maximum diastolic and diastolic blood vessel state of the blood vessel contained in the reference sample at the time of acquiring the relation function, do.

According to the bloodless blood glucose measurement method and the bloodless blood glucose measurement device of the present invention, since the relationship between the blood sugar level and the Raman scattering signal can be corrected based on the pulse wave amplitude of the blood vessel, Effect can be provided.

1 is a block diagram of a blood glucose measurement apparatus according to an embodiment of the present invention.
2 is a detailed view of a measuring unit according to an embodiment of the present invention.
FIG. 3 shows a flowchart of a blood glucose measurement method according to an embodiment of the present invention.
FIG. 4 shows the relationship between the blood sugar amount through blood sampling, the intensity of the Raman scattering signal, and the reference factor.
Figure 5 shows the Raman scattering spectrum.
6 shows the intensity of the Raman scattering signal according to the heartbeat period.
7 shows the intensity difference of the Raman scattering signal.
8 is a view for explaining a blood glucose measurement method according to another embodiment of the present invention.

The above objects, features and advantages of the present invention will become more apparent from the following detailed description taken in conjunction with the accompanying drawings. It is to be understood, however, that the invention is not limited to the disclosed embodiments, but, on the contrary, is intended to cover various modifications and similarities. Like reference numerals designate like elements throughout the specification. In the following description, well-known functions or constructions are not described in detail since they would obscure the invention in unnecessary detail. In addition, numerals (e.g., first, second, etc.) used in the description of the present invention are merely an identifier for distinguishing one component from another.

1 is a block diagram of a blood glucose measurement apparatus according to an embodiment of the present invention.

The blood glucose measurement apparatus 10 may include an interface unit 100, a control unit 200, a communication unit 300, a measurement unit 400, a storage unit 600, and an output unit 700. The components shown in FIG. 1 are not essential, and a blood glucose measurement device having more or less components than those shown in FIG. 1 may be implemented.

Hereinafter, the components will be described in order.

The interface unit 100 serves as a path for communication with all external devices connected to the blood glucose measurement device 10. [ The interface unit 100 receives data from an external device or supplies power to each component in the blood glucose measurement device 10 or allows data in the blood glucose measurement device 10 to be transmitted to an external device. For example, a wired / wireless headset port, an external charger port, a wired / wireless data port, a memory card port, a port for connecting a device having an identification module, an audio I / O port, A video input / output (I / O) port, an earphone port, and the like may be included in the interface unit 100.

In addition, the interface unit 100 may further include a user input unit. The user input unit may generate input data for controlling the operation of the blood glucose meter 10 by the user. The user input unit may include a key pad, a dome switch, a touch pad (static / static), a jog wheel, a jog switch, and the like.

The control unit 200 typically controls the overall operation of the blood glucose measurement apparatus 10. For example, the blood glucose measurement and the output of the measured blood glucose value. The control unit 200 may process the control signal generated through the user input unit.

The communication unit 300 can transmit the data generated by the blood glucose measurement device 10 to an external device, for example, medical equipment of a medical institution. Also, the communication unit 300 can receive necessary data from an external device. The communication unit 300 may include, for example, a wired and / or wireless communication module.

The measuring unit 400 may provide a function of measuring blood glucose. The specific configuration of the measuring unit 400 will be described below with reference to Fig.

The storage unit 600 may store a program for operation of the controller 200 and may store data generated by the blood glucose measurement apparatus 10 and data received from an external device through the communication unit 300. [ The storage unit 600 may be a flash memory type, a hard disk type, a multimedia card micro type, a card type memory (for example, SD or XD memory) (Random Access Memory), SRAM (Static Random Access Memory), ROM (Read Only Memory), EEPROM (Electrically Erasable Programmable Read-Only Memory), PROM A disk, and / or an optical disk. In addition, the blood glucose measurement apparatus 10 may operate in association with a web storage that performs a storage function of the memory unit 600 on the Internet.

The output unit 700 is for generating an output related to a visual, auditory or tactile sense. The output unit 700 may include a display unit, an audio output module, an alarm unit, and a haptic module.

2 is a detailed view of a measuring unit according to an embodiment of the present invention.

The measuring unit 400 can measure the blood glucose level using the Raman scattering method.

To facilitate understanding, the Raman scattering method used for measuring blood glucose will be described in detail as follows.

Raman scattering refers to a phenomenon in which, when a material is irradiated with light at a constant frequency, light having a frequency different from that of molecular natural vibration, rotational energy, or crystal lattice vibration energy is scattered. The phenomenon that a part of light travels in the other direction when light passes through a medium is called scattering. In particular, the process of scattering while losing or obtaining energy is called Raman scattering.

More specifically, light of a specific frequency irradiated toward an arbitrary substance loses or becomes short in frequency because energy is lost or obtained by molecular vibration inherent to the substance. The longer or shorter the frequency of light is scattered by a particular material is called the raman shift. In particular, since the Raman shift is caused by the inherent molecular vibration of the material, the degree of Raman shift differs for each material. Therefore, by measuring the Raman scattering light, it is possible to know what kind of material is. That is, when the Raman scattering of an arbitrary substance is measured in a state where information on the Raman shift inherent in the blood sugar is known, if the Raman shift becomes equal to the blood sugar, it can be understood that the arbitrary substance is the blood sugar.

Furthermore, it is possible to know how much blood sugar is contained in an arbitrary substance through Raman scattering. That is, by measuring the intensity of the Raman scattering signal scattered by blood sugar, the amount of blood sugar contained in an arbitrary substance can be measured.

Particularly, in the case of measuring the blood glucose level of the blood flowing into the blood vessel through the Raman scattering, the blood sampling method can be adopted. The bloodless blood may mean a method of measuring blood glucose without passing blood. For example, by using light that can penetrate the skin, the blood sugar amount of the blood in the skin can be measured.

The measurement unit 400 for measuring Raman scattering may include a light emitting unit 410, a lens 420, a spectroscope 430, and a light receiving unit 440.

The light emitting portion 410 may emit light toward the sample 500.

Here, the sample 500 may be a specific part of the human body. Particularly, the specific part of the human body may be, for example, a finger having many capillaries. The reason for measuring the capillary blood vessels is that the capillaries are located close to the skin layer, so that the light easily penetrates into the capillaries and the variation of the blood is relatively large according to the heartbeat period. It is because it receives greatly.

Hereinafter, a sample may include a target and a reference sample. The reference sample is used for acquiring the above-mentioned relation function, and the object may be one used for bloodless blood glucose measurement.

The light emitting portion 410 may be a lamp and / or a laser.

It may be desirable for the light to have near infrared radiation, for example, a period of 2 to 3 mm, which can penetrate deeply into the skin. Particularly, since the laser has strong light intensity and can pass through the skin layer, it has an advantage that it can easily obtain the Raman scattering signal.

The lens 420 can adjust the direction of light so that the light irradiated from the light emitting portion is focused at the position of the sample 500. Also, the direction of scattered light can be adjusted so that a scattered Raman scattering signal in the sample 500 can be directed to the spectroscope 430. [

The spectroscope 430 can disperse Raman signals scattered by the sample 500 by frequency. That is, the light emitted from the light emitting unit 410 may be scattered by the sample 500, and Raman shift may occur. As described above, the degree of Raman shift can be grasped and blood glucose can be measured, and the blood glucose level can be measured based on the intensity of the Raman shift signal corresponding to blood glucose. The spectroscope 430 disperses the scattered Raman scattering signal by the sample 500, thereby allowing the light receiving unit 440 to receive the spectroscopic Raman scattering signal.

The spectroscope 430 may be, for example, a prism and / or a grating.

The light receiving unit 440 can measure the Raman scattering signal that has been spectroscopically measured by the spectroscope 430. The light receiving unit 440 can transmit the intensity of the Raman scattering signal for each frequency to the controller 200. The controller 200 can acquire the intensity of the Raman scattering signal based on the measured Raman scattering signal. The intensity of the Raman scattering signal refers to the integral value of the Raman shifted Raman signal with respect to the frequency axis.

On the other hand, the light receiving unit 440 can sense scattered light that stoke, that is, scattered and lose energy in the Raman scattering signal. The Raman scattering signal can be measured even if the sensitivity of the light receiving unit 440 is low because the intensity of the Raman scattering signal that loses energy due to scattering is larger than the anti-stoke that obtains energy by scattering.

The control unit 200 can obtain the blood glucose level corresponding to the intensity of the Raman scattering signal received by the light receiving unit 440 based on the first relation function for each blood glucose amount corresponding to the intensity of the scatter signal. The first relation function may be stored in the storage unit 600 or received through the communication unit 300. The method for obtaining the first relational function between the blood glucose level and the Raman scattering signal intensity will be described in more detail.

Hereinafter, a blood glucose measurement method according to an embodiment of the present invention will be described in detail. The blood glucose measurement method according to an embodiment of the present invention may be implemented in the blood glucose measurement apparatus according to the embodiment of the present invention described above or may be implemented by a system having a different structure. However, for convenience of explanation, in explaining the blood glucose measurement method, reference is made to the configuration shown in FIG. 1 and FIG.

FIG. 3 shows a flowchart of a blood glucose measurement method according to an embodiment of the present invention. Referring to Fig. 3, reference can be made to Figs. 4 to 7. Fig. FIG. 5 shows the Raman scattering spectrum, FIG. 6 shows the intensity of the Raman scattering signal according to the pulsation period, FIG. 7 shows the intensity of the Raman scattering signal through the Raman scattering signal, It represents the intensity difference of scattering signal.

Since the order of each step described below is merely an arbitrary one, each step can be performed simultaneously in parallel, and the preceding step can be performed later than the following step.

<First Relative Function between Blood Sugar Through Blood Sampling and Strength of Reference Raman Scatter Signal and Acquisition of First Reference Factor>

Through blood collection, the amount of blood glucose contained in the blood can be measured (S310). In the following, step S310 may be referred to as a calibration step.

This step may be a step for acquiring a first relational function, for example, a b-vector, between the blood glucose level and the intensity of the reference Raman scattering signal for bloodless blood glucose measurement. That is, when the intensity of the Raman scattering signal is acquired by the bloodless blood glucose meter 10, the controller 200 can acquire the blood glucose level corresponding to the intensity of the Raman scattering signal through the first relation function.

The amount of blood glucose used when acquiring the relationship function can be used in the same terms as the reference blood glucose level. The reference Raman scattering signal may also be a term specifying the Raman scattering signal used in obtaining the relational function.

Referring to FIG. 4 for explaining the process of acquiring the first relation function, the blood sugar amount can be measured from a1 to a10 through a plurality of blood sampling from t1 to t10. As described above, blood glucose measurement through blood collection can be performed by a known method. Each blood sampling is performed at an arbitrary time, such as before a meal or after a meal, so the blood sugar levels a1 to a10 may be different values.

In addition, the intensity of the scattering signal can be measured only from the reference t1 to t10. The intensity of each reference Raman scattering signal can be measured at each of b1 to b10. Thus, only the reference blood glucose level a1 corresponds to the intensity b1 of the scatter signal, the reference blood glucose level a2 corresponds to the reference blood glucose r2, and the intensity b2 of the scatter signal is equivalent to the standard blood glucose level a2. It can be seen that the reference blood glucose amount a10 corresponds to the reference b and the intensity b10 of the scattering signal. Based on this, a first relation function between the reference blood glucose level and the intensity of the reference Raman scattering signal can be obtained.

The first relation function may be stored in the storage unit 600, received via the communication unit 300, and stored in the storage unit 600. [

At this time, in order to reduce the noise included in the Raman scattering signal, the duration of the Raman scattering signal measurement can be made longer than a certain time. That is, the relationship between the noise included in the Raman scattering signal and the signal to noise ratio (SNR) decreases with time. The arbitrary time may be 60 seconds or more. At this time, the duration of the Raman scattering signal measurement can be made the same in order to make the influence of the noise equal between t1 and t10.

On the other hand, since the degree of change of the blood vessel state varies depending on the heartbeat cycle and the surrounding environment, for example, the ambient temperature, the amount of blood glucose contained in the blood vessel may vary from hour to hour. That is, the shrinkage relaxation degree of the blood vessel at the time of acquiring the first relation function through blood collection and the relaxation degree of the blood vessel shrinkage at the time of measuring the Raman scattering signal through the blood sugar measurement apparatus 10 without blood collection method may be different , It is necessary to establish the relationship between the acquisition of the first relational function and the measurement of the Raman scattering signal through non-blood collection in order to improve the accuracy of blood glucose measurement.

For this purpose, when the reference Raman scattering signal is measured in step S310, the change of the scattered signal of the reference Raman by the heartbeat period can be measured. For example, in a normal adult, the heart is pulsed about 70 to 75 beats per minute, so it takes 0.8 to 0.86 seconds per beat. That is, when the reference Raman scattering signal is measured for a time longer than the one heartbeat period, the change in the reference Raman scattering signal according to the heartbeat period can also be measured.

Referring to FIG. 5, for example, when measuring the Raman scattering signal for one second, ten Raman scattering signals can be measured. This is because it is easy to find the maximum diastolic and systolic time of the blood vessels by measuring the Raman scattering signal more than 10 times per second when considering the heartbeat period.

Referring to FIG. 6, a method for obtaining information on the degree of contraction and relaxation of a blood vessel at the time of acquiring the first relational function can be known. That is, the x-axis represents time, and the y-axis represents the integral value for each frequency of the Raman scattering signal for each time. That is, when the intensity of the Raman scattering signal is RS1, since the intensity of the Raman scattering signal is the smallest, it can be regarded as the maximum systolic phase of the blood vessel with the smallest blood sugar amount. When the intensity of the Raman scattering signal is RS2, Since it is the largest, it can be regarded as the maximum dilator of the blood vessel which has the highest blood sugar amount. RS1 may be an integral value of a certain Raman scattering signal shown in FIG. 5 with respect to the frequency axis as described above.

The difference between RS2 and RS1 can be seen as the first reference factor associated with relaxation of the vessels. That is, referring again to FIG. 4, it is possible to measure the first reference factor c1 at t1, measure the first reference factor c2 at t2, and measure the first reference factor c10 at t10 . At this time, the average value of the first reference factors c1 to c10 can be selected as the representative first reference factor. The representative reference factor can be selected by various methods such as the average of all the values, and the average of the remaining values except for the largest value and the smallest value. The first reference factor in the following can refer to a representative reference factor.

Through the above process, a first relation function between the standard blood glucose level and the standard Raman scattering signal intensity and a first reference factor for the blood glucose level correction according to the beating cycle of the blood vessel can be measured. In addition, the above process may be implemented in the blood glucose measurement apparatus 10 according to an embodiment of the present invention, and may be measured in another blood glucose measurement apparatus. At this time, the first relation function and the first reference factor may be transmitted to the communication unit 300 of the blood glucose measurement apparatus 10 as described above, and stored in the storage unit 600.

&Lt; Raman scattering signal through non-blood collection &lt;

The measuring unit 400 can measure the intensity of the Raman scattering signal of the sample 500 in a non-blood collecting manner (S320). In the following, step S320 may be referred to as a prediction step.

The measurement of the Raman scattering signal can be roughly divided into two measurements. The first is the intensity value of the Raman scattering signal to be substituted into the first relation function, the second is the intensity value of the first Raman scattering signal to be compared with the first reference factor in order to correct the blood sugar amount error in accordance with the difference between the maximum diastole of the blood vessel and the maximum systolic time of the blood vessel. It can be seen that the correction factor is measured.

First, the intensity of the Raman scattering signal for substituting into the first relation function will be described in detail as follows. The time for measuring the Raman scattering signal and the time for measuring the intensity of the Raman scattering signal in step S320 may be the same to obtain the first relation function in step S310. This is because the noise contained in the Raman scattering signal tends to decrease substantially in accordance with the measurement time, so that the amount of noise to be reduced is equalized.

That is, the measuring unit 400 can measure the Raman scattering signal for the same time as the Raman scattering signal measurement time, which is the same as in the calibration step.

Second, in order to correct the blood sugar amount error due to the difference between the maximum diastole of the blood vessel and the maximum systolic time of the blood vessel, the first correction factor will be described in detail with reference to FIG.

The two graphs shown in FIG. 7 represent the intensity of the Raman scattering signal according to each time. L1 represents a graph of shrinkage relaxation of blood vessels obtained in the calibration step, and L2 represents a graph of shrinkage relaxation of the blood vessels measured in the prediction step.

As shown, the difference between the maximum diastolic and the maximum systolic at the calibration step may be different from the difference between the maximum diastolic and the maximum systolic at the prediction stage. For example, the difference in blood vessel diameter between the maximal systolic and maximal diastolic vessels in the calibration phase may be 1.5 mm, and the difference in vessel diameter between the maximal systolic and maximal diastolic vessels in the prediction stage may be 1.0 mm.

The first correction factor may be obtained to correct the blood glucose amount error caused by the thickness difference of the blood vessels. On the other hand, the first correction factor may be measured in the same manner as the first reference factor. That is, the first correction factor may be a difference value between the maximum systolic blood pressure at the prediction step and the intensity of the Raman scattering signal at the maximum blood vessel dilation period.

That is, the measuring unit 400 can measure the Raman scattering signal of the sample 500 and the first correction factor by the non-blood-collecting method.

&Lt; Obtaining a blood glucose level from the first relation function based on a first reference factor and a first correction factor >

The controller 200 may acquire the blood glucose level from the first relation function based on the difference between the first reference factor and the first correction factor (S330).

The controller 200 may compare the first reference factor and the first correction factor.

If the first reference factor is greater than the first correction factor, it means that the difference between the maximum diastolic time of the vessel and the maximum systolic time of the vessel in the calibration step is greater than the difference between the maximum diastole of the vessel and the maximum systolic time of the vessel can do.

Therefore, the controller 200 can largely correct the intensity of the Raman scattering signal measured in the prediction step and substitute the first correlation function for the first reference factor and the first correction factor.

Also, the controller 200 can substitute the intensity of the Raman scattering signal measured at the prediction step into the first relational function, and correct the obtained blood sugar amount to a larger extent.

The degree of correction can be easily changed by a person skilled in the art.

On the other hand, when the first reference factor is smaller than the first correction factor, the difference between the maximum diastole of the blood vessel and the maximum systolic time of the blood vessel in the calibration step is smaller than the difference between the maximum diastole of the blood vessel and the maximum systolic time of the blood vessel in the prediction step It can mean that.

Therefore, the controller 200 may correct the intensity of the Raman scattering signal measured in the prediction step to a small value and substitute the intensity of the Raman scattering signal into the first relation function, thereby correcting the difference between the first reference factor and the first correction factor.

In addition, the controller 200 may substitute the intensity of the Raman scattering signal measured in the prediction step into the first relational function and correct the acquired blood sugar amount to be smaller.

Therefore, it is possible to easily measure blood sugar through bloodless blood collection, and at the same time, it is possible to reduce an error caused by a change in the pulse wave amplitude of the blood vessel.

In addition, the control unit 200 can output the corrected blood sugar amount through the output unit 700, and can transmit the corrected blood sugar amount to the external device through the communication unit 300. If the corrected blood glucose level is smaller than or greater than a specific value, the controller 200 determines that there is a problem with the blood glucose level of the subject and may be programmed so that the controller 200 can automatically transmit the blood glucose level to the external device without inputting by the user .

Through the above steps, it is possible to determine the internal and external factors of the subject, such as the pre-meal, post-meal, post-exercise, post-exercise awareness, and the like, And correct blood glucose level can be measured.

8 is a view for explaining a blood glucose measurement method according to another embodiment of the present invention. The method of obtaining at least one of the embodiment and the first relation function, the first reference factor, and the first correction factor may be different.

The blood glucose measurement apparatus 10 may be configured to additionally measure a photoelectric pulse wave (PPG) of the sample 500. [ The negative pulse wave is a photoelectric pulse wave. The volumetric pulse wave is a method of extracting information related to the heartbeat using a predetermined number of LEDs and a photodetector. Heart rate detection using volume pulse waves is a simple sensor module that can measure the photoelectrical pulse wave through a single point of contact with the body.

The measuring unit 400 may further include an LED and a photodetector for measuring the volume pulse wave.

A method of obtaining the second relation function, which is in contrast to the first relation function, using the volumetric pulse wave will be described in detail as follows.

In the calibration step of S310, the intensity of the scattering signal and the intensity of the reference Raman scattering signal in the maximum vasoconstrictor of the blood vessel maximum diastolic time included in the reference sample can be obtained by using the volume pulse wave, respectively.

8, a second relation function between the reference Raman scattering signal intensity and the reference Raman scattering signal intensity at the maximum vasoconstricting time can be obtained. Therefore, the influence of the Raman scattering signal due to the tissue of the sample in the vascular maximum systolic period can be minimized. By minimizing the Raman scattering signal due to the texture of the sample, it is possible to provide an effect of improving the sensitivity of the Raman scattering signal measurement.

More specifically, when obtaining the second relation function, the second relation function can be obtained more precisely by removing the intensity of the Raman scattering signal associated with the tissue included in the sample and amplifying the intensity of the remaining Raman scattering signal.

In the case of using the second relation function, in the prediction step of S320, the controller 200 compares the intensity of the Raman scattering signal at the maximum volumetric pulse wave of the subject and the Raman scattering at the minimum volumetric pulse wave The difference of the intensity of the signal can be obtained.

At this time, the controller 200 can correct the blood glucose level using the first reference factor, the first correction factor, and the second correlation function related to the maximum systolic and the minimum systolic time of the blood vessel.

Further, a second reference factor and a second correction factor may be used in place of the first reference factor and the first correction factor in consideration of the volumetric pulse wave.

The second reference factor obtained in the calibration step is the difference between the maximum pulsation amplitude and the minimum pulsation amplitude over time. That is, since the difference between the maximum pulsation size and the minimum pulsation size of the sample can be obtained through the volumetric pulse wave, it can be used as a reference factor for correcting the blood sugar amount difference according to the change of the pulse wave period of the blood vessel.

In addition, in the prediction step, the controller 200 may acquire a second correction factor by obtaining a difference between a maximum pulsation size and a minimum pulsation size of the sample 500. Accordingly, the control unit 200 can correct the blood glucose level obtained by comparing the second reference factor stored in the storage unit 600 or the second reference factor received through the communication unit 300 with the second correction factor. The control unit 200 compares the second reference factor with the second correction factor to correct the blood glucose level can be performed in the same manner as correcting the blood glucose level based on the first reference factor and the first correction factor described in the embodiment have.

On the other hand, the blood glucose measurement apparatus 10 can acquire the blood glucose level based on the first relation function, the second reference factor, and the second correction factor, and as described above, the second relation function, the first reference factor, The blood glucose level can be obtained based on the factor, and the blood glucose level can be obtained based on the second relation function, the second reference factor, and the second correction factor.

It will be apparent to those skilled in the art that various modifications and variations can be made in the present invention without departing from the spirit and scope of the invention as defined by the appended claims. Accordingly, such modifications or variations are intended to fall within the scope of the appended claims.

10: blood glucose meter 200:
400: measuring part 500: sample

Claims (18)

A measuring unit for measuring a Raman scattering signal of a target object; And
Acquiring the intensity of the measured Raman scattering signal, acquiring a correction factor based on changes in the maximum diastolic and diastolic blood vessel states of the blood vessels included in the subject,
And a controller for obtaining a blood glucose level using the relational function based on a comparison value of the reference factor, the correction factor, and the intensity of the Raman scattering signal at the time of acquiring the relation function,
The relation function represents a relationship between the intensity of the scatter signal and the reference blood glucose level of the reference sample only with respect to the reference measured with respect to the reference sample,
Wherein the reference factor is obtained on the basis of a change in a maximum diastolic and a maximum systolic blood vessel state of the blood vessel included in the reference sample at the time of acquiring the relational function. delete The method according to claim 1,
Further comprising a communication unit and a storage unit,
Wherein the relational function and the reference factor are received via the communication unit and stored in the storage unit
Bloodless blood glucose measuring device. The method according to claim 1,
Wherein the measurement duration of the Raman scattering signal and the reference Raman scattering signal is the same
Bloodless blood glucose measuring device. 5. The method of claim 4,
And the measurement duration of the Raman scattering signal and the reference Raman scattering signal is 60 seconds or more.
Bloodless blood glucose measuring device. The method according to claim 1,
Wherein the intensity of the Raman scattering signal is an integral value with respect to a frequency axis of the Raman scattering signal and the intensity of the reference Raman scattering signal is an integral value with respect to a frequency axis of the scattering signal only with the reference Raman
Bloodless blood glucose measuring device. The method according to claim 1,
Wherein the measuring unit measures the Raman scattering signal with a period shorter than the heartbeat period
Bloodless blood glucose measuring device. The method according to claim 1,
Wherein the measuring unit measures the Raman scattering signal at least 10 times per second
Bloodless blood glucose measuring device. The method according to claim 6,
The reference factor may be,
The reference R is the difference between the maximum value and the minimum value of the intensity of the scattering signal,
Wherein the correction factor
And a difference between a maximum value and a minimum value of the intensity of the Raman scattering signal
Bloodless blood glucose measuring device. The method according to claim 1,
Wherein the measuring unit further measures a volume pulse wave of the subject,
The intensity of the Raman scattering signal,
And an integration value for the frequency axis of the Raman scattering signal in the measured maximum VLP when the Raman scattering signal is measured, and an integration value for the frequency axis of the RAN scattering signal in the measured minimum VLP,
The intensity of the reference Raman scattering signal is,
Wherein the reference pulse is the difference between the integrated value of the reference pulse only on the frequency axis of the scattering signal and the integral value of the reference pulse only on the frequency axis of the scattering signal in the minimum excitation pulse wave in the maximum excitation pulse wave of the reference sample, doing
Bloodless blood glucose measuring device. The method according to claim 1,
Wherein the measuring unit further measures a volume pulse wave of the subject,
The reference factor may be,
A difference value between the maximum and minimum volume pulse waves of the reference sample at the time of acquiring the relation function,
Wherein the correction factor
And a difference between a maximum volumetric pulse wave and a minimum volumetric pulse wave of the subject at the time of measuring the Raman scattering signal
Bloodless blood glucose measuring device. The method according to claim 9 or 11,
If the reference factor is greater than the correction factor,
The intensity of the Raman scattering signal is largely corrected to a predetermined magnitude and is substituted into the relational function to obtain the blood sugar amount or the intensity obtained by substituting the intensity of the Raman scattering signal into the relation function is corrected to a predetermined magnitude And acquiring the blood glucose level
Bloodless blood glucose measuring device. The method according to claim 9 or 11,
When the reference factor is smaller than the correction factor,
The intensity of the Raman scattering signal is corrected so as to be small to a predetermined size, and the result is substituted into the relational function to obtain the blood sugar amount or the intensity of the Raman scattering signal to the relation function, And a blood glucose level is obtained
Bloodless blood glucose measuring device. delete Measuring a Raman scattering signal of the object;
Obtaining an intensity of the measured Raman scattering signal;
Obtaining a correction factor based on changes in a maximum diastolic and a systolic blood vessel state of the subject included in the subject;
Comparing the reference factor and the correction factor when acquiring the relation function; And
Obtaining a blood glucose level using the relational function based on the result of the comparison step and the intensity of the Raman scattering signal,
The relation function represents a relationship between the intensity of the scatter signal and the reference blood glucose level of the reference sample only with respect to the reference measured with respect to the reference sample,
Wherein the reference factor is obtained on the basis of a change in a maximum diastolic and a maximum systolic blood vessel state of the blood vessel contained in the reference sample at the time of acquiring the relation function.
How to measure bloodless blood sugar. The method of claim 15, wherein
The intensity of the Raman scattering signal and the intensity of the reference Raman scattering signal,
An integral value of a frequency axis of the Raman scattering signal and the reference Raman scattering signal,
The reference factor may be,
The reference R is the difference between the maximum value and the minimum value of the intensity of the scattering signal,
Wherein the correction factor
And a difference between a maximum value and a minimum value of the intensity of the Raman scattering signal
How to measure bloodless blood sugar. 16. The method of claim 15,
Further comprising the step of measuring a volumetric pulse wave of the subject,
The intensity of the Raman scattering signal,
And an integration value for the frequency axis of the Raman scattering signal in the measured maximum VLP when the Raman scattering signal is measured, and an integration value for the frequency axis of the RAN scattering signal in the measured minimum VLP,
The intensity of the reference Raman scattering signal is,
Wherein the reference pulse is the difference between the integrated value of the reference pulse only on the frequency axis of the scattering signal and the integral value of the reference pulse only on the frequency axis of the scattering signal in the minimum excitation pulse wave in the maximum excitation pulse wave of the reference sample, doing
How to measure bloodless blood sugar. 16. The method of claim 15,
Further comprising the step of measuring a volumetric pulse wave of the subject,
The reference factor may be,
A difference value between the maximum and minimum volume pulse waves of the reference sample at the time of acquiring the relation function,
Wherein the correction factor
And a difference between a maximum volumetric pulse wave and a minimum volumetric pulse wave of the subject at the time of measuring the Raman scattering signal
How to measure bloodless blood sugar.

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