KR101656746B1 - Apparatus and method for correcting blood glucose concentration - Google Patents

Abstract

The present invention relates to an apparatus and method for correcting a blood glucose concentration, and more particularly, to an apparatus and method for correcting a blood glucose concentration by receiving a PPG signal of a blood vessel of a patient and an actually measured reference blood glucose concentration of the patient and an optical signal obtained by irradiating light to a predetermined body region of the patient , The correction method of the present invention for correcting the blood glucose concentration of the optical signal includes a step of performing a correction for dividing the optical signal by the area of the AC portion of the PPG signal and comparing the reference blood glucose concentration and the PPG signal And the corrected signal is subjected to PLS processing to establish a correction model for blood glucose concentration and PLS processing of the corrected signal and the corrected optical signal to correct the blood glucose concentration . According to the present invention, accurate blood glucose concentration can be obtained by correcting the blood glucose concentration in consideration of the volume change of the blood vessel.

Description

[0001] APPARATUS AND METHOD FOR CORRECTING BLOOD GLUCOSE CONCENTRATION [0002]

The present invention relates to an apparatus and method for correcting blood glucose concentration, and more particularly, to an apparatus and method for correcting blood glucose concentration used in a bloodless blood glucose measurement system.

Non-invasive measurement techniques for the prevention, diagnosis and management of diseases are currently one of the areas of active research. Especially, bloodless blood sugar measurement is of great importance in relation to diabetes, which has recently increased in incidence.

In general, an optical measuring method, a reverse ion osmosis method, an impedance measuring method, and an electrophoresis method have been proposed for bloodless blood glucose measurement. Among these, optical measurement methods, which are especially studied, are to estimate blood glucose concentration through signals obtained by scanning light of a certain wavelength band. These optical measurement methods are classified into NIR spectroscopy, MIR spectroscopy, Raman spectroscopy, and photoacoustic spectroscopy according to the light used again.

In the conventional optical measuring method as described above, since the optical signal is affected by changes in the living body, the estimated blood glucose concentration through the optical signal is also affected, which causes an error in the blood glucose concentration estimation, There is a problem that it is difficult to estimate the concentration.

On the other hand, one of the in vivo changes that affect the blood glucose concentration estimation is the perturbation of the blood vessel and consequently the volume change of the blood vessel. Partial Least Square (PLS) method is widely used as a tool for analyzing an optical signal obtained from an optical measurement method. Conventionally, concentration estimation using a PLS process includes optical signals There is a problem in that an error occurs because the amount of the blood glucose signal in the blood vessel changes depending on the volume change of the blood vessel.

Disclosure of Invention Technical Problem [8] The present invention has been proposed in order to solve the above-mentioned problems, and it is an object of the present invention to provide a bloodless blood glucose measurement system using an optical measuring method, in which blood glucose concentration is corrected in consideration of volume change of blood vessels due to pulsation, And an object of the present invention is to provide a concentration correction apparatus and method.

In order to achieve the above object, an optical signal obtained by irradiating light on a predetermined body part of a patient using a PPG signal of a blood vessel of a patient and an actually measured reference blood glucose concentration of the patient, The correction device of the present invention for correcting the blood glucose concentration of the PPG signal comprises: a first correction unit for performing a correction for dividing the optical signal by the area of the portion (AC portion) where the change of the PPG signal is present; A setup unit for establishing a calibration model for blood glucose concentration using the reference blood glucose concentration; And a second correction unit for performing a partial least squares (PLS) process on the correction model established by the setting unit and the optical signal corrected by the first correction unit to perform correction of blood glucose concentration, It is preferable to further include a preprocessing unit for performing a preprocessing using any one of a background removal method using a principal component analysis (PCA) method, an independent component analysis (ICA) method, and a non-numerical factor factorization (NMF) .

Here, the establishing unit may include: a third correcting unit for performing a correction for dividing the optical signal by the area of the AC portion of the PPG signal; And a generation unit for generating a correction model by PLS-processing the reference blood glucose concentration and the third correction unit-corrected optical signal, wherein the background removal method, the PCA method, and the ICA method And a pre-processing unit for performing pre-processing using any one of the NMF methods.

It is also possible to provide a blood glucose analyzer that receives a PPG signal of a blood vessel of a patient, an actually measured reference blood glucose concentration of the patient, and an optical signal obtained by irradiating light to a predetermined body part of the patient, , The correction method of the present invention includes the steps of: performing correction to divide the optical signal by the area of the AC portion of the PPG signal; A step of PLS-processing a signal obtained by performing a correction for dividing the reference blood glucose concentration and the optical signal by the area of the AC portion of the PPG signal to establish a correction model for blood glucose concentration; And performing PLS processing on the correction model and the optical signal on which the correction is performed to perform correction of blood glucose concentration.

On the other hand, in order to correct the blood glucose concentration of an optical signal obtained by irradiating light on a predetermined body part of the patient using the PPG signal of the patient's blood vessel and the actually measured reference blood glucose concentration of the patient, The apparatus comprises: an establishment unit for establishing a correction model for blood glucose concentration using the reference blood glucose concentration; An estimating unit for estimating blood glucose concentration by PLS processing the optical signal and the correction model established by the establishing unit; And a first correction unit for performing a correction for dividing an area of the AC portion of the PPG signal by the estimated part and a blood sugar concentration estimated by the estimation part, wherein a background removal method using a polynomial fitting, a PCA method, an ICA method And a pre-processing unit for performing pre-processing using any one of the NMF methods.

Here, the establishing unit may include: a second correcting unit for performing the correction on the reference blood glucose concentration by multiplying the reference blood glucose concentration by the area of the AC portion of the PPG signal; And a generation unit for generating a correction model by PLS-processing the output signal of the second correcting unit and the optical signal, wherein the background elimination method using the polynomial fitting, the PCA method, the ICA method, And a pre-processing unit for performing pre-processing using any one of the NMF methods.

It is also possible to provide a blood glucose analyzer that receives a PPG signal of a blood vessel of a patient, an actually measured reference blood glucose concentration of the patient, and an optical signal obtained by irradiating light to a predetermined body part of the patient, , The correction method of the present invention comprises a step of PLS-processing a signal obtained by performing a correction for multiplying the reference blood glucose concentration and the area of the AC portion of the PPG signal and the optical signal to establish a correction model for blood glucose concentration; Performing PLS on the optical signal and the correction model to estimate blood glucose concentration; And performing correction of the blood glucose concentration by dividing the estimated blood glucose concentration by the area of the AC portion of the PPG signal.

The present invention as described above has the effect of enabling accurate blood glucose concentration to be obtained by correcting the blood glucose concentration in consideration of the volume change of blood vessels in the bloodless blood glucose measurement system.

1 is an example of a bloodless blood sugar system to which the present invention is applied,
FIG. 2 is a structural view of a blood glucose concentration correcting apparatus according to a first embodiment of the present invention,
FIG. 3 is a detailed structural diagram of an embodiment of the correction model establishing unit of FIG. 2;
FIG. 4 is a flowchart of a first embodiment for explaining a blood glucose concentration correction method according to the present invention;
5A is an example of a PPG signal outputted by the PPG signal measuring unit of FIG. 2,
5B is an example of a spectrum of an optical signal input to the correction device of the present invention,
FIG. 5C is an example of a spectrum of a signal output by the preprocessing unit of FIG. 2,
FIG. 5D is an example of a spectrum of a signal outputted from the optical signal correcting unit of FIG. 2,
FIG. 5E is an example of a spectrum of the reference blood glucose concentration input to the correction model generation unit of FIG. 3,
FIG. 5F is an example of an output signal of the correction model generation unit of FIG. 3,
FIG. 5G is an example of the concentration of blood glucose in which the blood glucose concentration correcting unit of FIG.
6 is a structural view of a second embodiment of a blood glucose concentration correcting device according to the present invention,
FIG. 7 is a detailed structural diagram of one embodiment of the correction model establishing unit of FIG. 6;
FIG. 8 is a flowchart of a second embodiment for explaining the method of correcting blood glucose concentration according to the present invention.
FIG. 9A is an example of a PPG signal outputted by the PPG signal measuring unit of FIG. 6,
9B is an example of a spectrum of an optical signal input to the correction device of the present invention,
FIG. 9C is an example of a spectrum of a signal output by the preprocessing unit of FIG. 6,
FIG. 9D is an example of a spectrum of a reference blood glucose concentration input to the reference blood glucose concentration correction unit of FIG. 7,
FIG. 9E is an example of an output signal of the reference blood glucose concentration correction unit of FIG. 7,
FIG. 9F is an example of an output signal of the correction model generation unit of FIG. 7,
FIG. 9G is an example of an output signal of the blood glucose level estimating unit of FIG. 6,
FIG. 9H is an example of an output signal of the blood glucose concentration correcting unit of FIG. 6; FIG.

Hereinafter, a preferred embodiment of the present invention will be described in detail with reference to the accompanying drawings.

1 is a diagram illustrating an example of a bloodless blood sugar system to which the present invention is applied. The present invention is applied to signal processing of an optical signal finally output in a system using Raman spectroscopy. In FIG. 1, measurement of blood glucose in a finger of a patient will be described as an example. However, the present invention is not limited to the above-described measurement, and measurement of blood sugar with respect to other parts of the body, such as measurement using an arm, is not excluded. It should be apparent to those skilled in the art that the present invention is not limited to acquiring an optical signal using the Raman spectroscopy system and that an optical signal can be acquired through another measurement system .

As shown in the drawing, a system to which the present invention is applied may use a light source 102 emitting light, for example, an 830 nm diode laser. The beam 106 output from the light source 102 is passed through a bandpass filter 104 and is then passed through a focusing lens 108 and a prism 110 to form a paraboloidal mirror, (112). The light backscattered by the parabolic mirror 112 is condensed through a notch filter 114 and a focusing lens 116.

The blood glucose concentration correcting apparatus 10 of the present invention can measure an accurate blood glucose level by using the optical signal related to the condensed blood glucose as described above. However, other devices used for collecting optical signals in the above system may be further included, but the description thereof will be omitted in the description of the present invention since it is obvious in the technical field of the present invention.

With respect to the optical signal output as described above, the blood glucose concentration correcting apparatus of the present invention corrects the blood glucose concentration in consideration of the volume change of the blood vessel. Hereinafter, an apparatus and method for correcting blood glucose concentration according to the present invention will be described with reference to the drawings.

FIG. 2 is a structural view of a blood glucose concentration correcting device according to a first embodiment of the present invention, which illustrates a method of correcting a measured optical signal.

As shown in the figure, the blood glucose concentration correcting apparatus 10 of the present invention includes a blood flow measuring unit 12, a preprocessing unit 14, A blood glucose concentration correcting unit 18, and a correction model establishing unit 20, as shown in FIG.

The PPG signal measurement unit 12 is responsible for measuring the PPG signal of the patient's blood vessel. The PPG signal measured by the PPG signal measuring unit 12 refers to a physiological signal for measuring a blood flow waveform in a peripheral blood vessel, through which pulsation and volume change of a blood vessel can be deduced. The PPG signal can be obtained using a pulse oximeter, which usually measures light absorption by applying light to the skin. That is, the PPG signal measuring unit 12 of FIG. 2 may be a pulse oximeter. Detailed operation of the pulse oximeter is well known in the technical field to which the present invention belongs, and a detailed description thereof will be omitted. 5A is an example of a PPG signal output from the PPG signal measuring unit 12 of FIG.

The preprocessing unit 14 preprocesses the input optical signal. For the preprocessing, a background subtraction may be performed using a polynomial fitting. Polynomial fitting refers to finding a polynomial closest to the original signal and removing the signal obtained through polynomial fitting in the original signal. That is, when the original optical signal is denoted by 'X' and the polynomial obtained through polynomial fitting is referred to as 'polynomial', the signal output by the preprocessing unit 14 is equal to 'X-polynomial'. The principle of the polynomial fitting and the detailed description thereof are well known in the technical field of the present invention, and a detailed description thereof will be omitted. FIG. 5B is an example of a spectrum of an optical signal input to the correction apparatus of the present invention, and FIG. 5C is an example of a spectrum of a signal output by the preprocessing unit 14 of FIG. 5B is the input signal of the preprocessor 14, and the graph of FIG. 5C may be the output signal of the preprocessor 14. However, the background removal method using polynomial fitting has been described as the pre-processing performed by the preprocessing unit 14 of the present invention. However, the present invention is not limited thereto, and principal component analysis (hereinafter simply referred to as " (Hereinafter, simply referred to as 'ICA') method and a non-negative matrix factorization (hereinafter referred to simply as 'NMF') method, And may not perform the preprocessing.

The optical signal correcting unit 16 of Fig. 2 corrects the optical signal which has undergone the preprocessing by the preprocessing unit 14 or which has not undergone the preprocessing, according to the PPG signal measured by the PPG signal measuring unit 12 It is responsible for performing functions. Referring to FIG. 5A, the PPG signal can be divided into an AC portion in which a change is present in a signal and a DC portion in which a change does not exist. Since the area of the AC portion (that is, the portion hatched in FIG. 5A) is proportional to the volume of the blood vessel, the optical signal correcting unit 16 divides the input optical signal by the area of the AC portion of the PPG signal to perform correction do. By such a correction, the signal related to the blood glucose present in the optical signal becomes proportional to the actual blood glucose concentration value. 5D is an example of a spectrum of a signal output from the optical signal correcting unit 16 of FIG.

The calibration model establishing unit 20 of FIG. 2 takes charge of establishing a model for correcting the blood glucose concentration using the actually measured reference blood glucose concentration at the time of establishing the calibration model. This will be described in more detail with reference to FIG.

3 is a detailed structural diagram of one embodiment of the correction model establishment unit of FIG. 2 includes a PPG signal measuring section 22, a preprocessing section 24, an optical signal correcting section 26, and a correction model generating section 28 . The PPG signal measuring unit 22, the preprocessing unit 24 and the optical signal correcting unit 26 of the correction model setting unit 20 are connected to the PPG signal measuring unit 12, the preprocessing unit 14, It may be a separate configuration from the portion 16, or it may be measured at a different time in the same configuration. Since this is the same as described above, a detailed description thereof will be omitted.

The signal input to the correction model generation unit 28 is a reference blood glucose concentration which is an actual measurement value obtained by an output signal of the optical signal correction unit 26 and actual blood collection. The reason for using such a reference blood glucose concentration is that once the concentration of the optical signal is measured, the relationship between the concentration and the signal can be estimated based on the concentration. The correction model generation unit 28 of the present invention performs well-known PLS processing, and a detailed description thereof will be omitted. FIG. 5E is an example of a spectrum of the reference blood glucose concentration input to the correction model generation unit 28 of FIG. 3, and FIG. 5F is an example of an output signal of the correction model generation unit 28 of FIG.

The blood glucose concentration correction unit 18 of FIG. 2 receives signals from the optical signal correction unit 16 and the correction model setting unit 20, respectively, and serves to correct the blood glucose concentration. FIG. 5G is an example of the blood glucose concentration at which the correction output from the blood glucose concentration correction unit 18 of FIG. 2 is performed. The blood glucose concentration correction unit 18 of the present invention can perform PLS processing on an input signal.

Hereinafter, the method for correcting the blood glucose concentration of the present invention will be described with reference to FIG. 4 is a flowchart of a first embodiment for explaining a method of correcting blood glucose concentration according to the present invention. Examples of output signals at each step are shown in Figs. 5A to 5G.

As shown in the drawing, the method of the present invention receives an optical signal measured in a bloodless blood sugar system (S41), and receives a reference blood glucose concentration, which is a concentration at the time when the optical signal is measured (S43). S41 and S43 do not describe the time-series order, but can be executed sequentially (independently of the order) or independently of each other. The reference blood glucose concentration is the concentration of blood glucose directly measured by blood collection as described above. Then, the PPG signal measuring unit 12 measures the PPG signal of the patient's blood vessel (S45). As described above, the PPG signal measuring unit 12 may be a pulse oximeter, and a detailed description of the operation of the pulse oximeter will be omitted.

The method of the present invention performs preprocessing using any one of a method of performing background removal using polynomial fitting, a PCA method, an ICA method, and an NMF method with respect to a received optical signal (S47). The above method is described above. However, although S47 has been described after S45 for the sake of convenience, S47 may be performed before S45, and S47 may not be performed, as described above.

In the method of the present invention, correction is performed according to the PPG signal for an optical signal that has undergone the preprocessing by S47 or has not undergone the preprocessing (S49). Specifically, correction is performed to divide the optical signal, which has undergone the pre-processing or the non-preprocessing, by the area of the AC portion of the PPG signal. Thereafter, the blood glucose concentration is corrected in the optical signal corrected by S49 using the correction model generated using the reference blood glucose concentration (S51).

In the blood glucose concentration correction using the correction model of S51, the generation of the correction model is performed by preprocessing the received optical signal by the same procedure as S47 (though the preprocessing may not be performed) A signal is measured to perform a correction for dividing an optical signal that has undergone pre-processing or not subjected to a preprocessing operation into an area of an AC portion of the PPG signal, performs a PLS process on the corrected optical signal and the reference blood glucose concentration, . The correction of S51 is to perform PLS processing with the correction model and the optical signal corrected by the PPG signal as an input. Thus, the blood glucose concentration accurately corrected can be obtained.

FIG. 6 is a structural diagram of a second embodiment of a blood glucose concentration correcting apparatus according to the present invention, which illustrates a method of correcting blood glucose concentration.

As shown in the figure, the blood glucose concentration correcting apparatus 10 of the present invention includes a PPG signal measuring unit 62, a preprocessing unit 64, a blood glucose concentration estimating unit 66, a blood glucose concentration correcting unit 68, And a model setting unit 70. [

The PPG signal measuring unit 62 functions to measure the PPG signal of the patient's blood vessel. The PPG signal refers to a physiological signal that measures the blood flow waveform in the peripheral blood vessels, and through this, pulsation and volume change of the blood vessel can be deduced. The PPG signal can be obtained using a pulse oximeter, which usually measures the change in light absorption by applying light to the skin. The PPG signal measuring unit 62 in FIG. 6 may be a pulse oximeter. Detailed operation of the pulse oximeter is well known in the technical field to which the present invention belongs, and a detailed description thereof will be omitted. 9A is an example of a PPG signal outputted by the PPG signal measuring unit 62 of FIG.

The preprocessing unit 64 preprocesses the input optical signal. As for the preprocessing, it is possible to perform the background removal using the polynomial fitting. Polynomial fitting refers to finding polynomials that are closest to the original signal and removing signals obtained through polynomial fitting in the original signal. The principle of the polynomial fitting and the detailed description thereof are well known in the technical field of the present invention, and a detailed description thereof will be omitted. FIG. 9B is an example of a spectrum of an optical signal input to the correction apparatus of the present invention, and FIG. 9C is an example of a spectrum of a signal output by the preprocessing unit 64 of FIG. 9B is an input signal of the preprocessing unit 64, and FIG. 9C is an output signal of the preprocessing unit 64. FIG. However, the background removal technique using polynomial fitting has been described as a pre-processing performed by the preprocessing unit 64 of the present invention. However, the present invention is not limited thereto, and a PCA method, ICA method, NMF method or the like widely known in the art can be used And may not perform the preprocessing.

The correction model establishing unit 70 of FIG. 6 takes charge of establishing a model for correcting the blood glucose concentration using the actually measured reference blood glucose concentration at the time of establishing the correction model. This will be described in more detail with reference to FIG.

7 is a detailed structural diagram of one embodiment of the correction model establishing unit of FIG.

As shown in the figure, the correction model establishing unit 70 of the present invention includes a PPG signal measuring unit 72, a preprocessor 74, a reference blood glucose concentration correction unit 76, and a correction model generating unit 78 . The PPG signal measuring section 72 and the preprocessing section 74 of the correction model establishing section 70 may be configured separately from the PPG signal measuring section 62 and the preprocessing section 64 of FIG. Lt; / RTI > Since this is the same as described above, a detailed description thereof will be omitted.

The signal input to the reference blood glucose concentration correction unit 76 is a reference blood glucose concentration which is an actual measurement value obtained by actual blood collection at the time of establishing the PPG signal and the correction model. The reason for using such a reference blood glucose concentration is that once the concentration of the optical signal is measured, the relationship between the concentration and the signal can be estimated based on the concentration. The reference blood glucose concentration correction unit 76 regards the area under the changed portion (AC portion) of the PPG signal as being proportional to the volume of the blood vessel, and performs the correction by multiplying the reference blood glucose concentration by the area of the AC portion of the PPG signal do. FIG. 9D is an example of a spectrum of the reference blood glucose concentration input to the reference blood glucose concentration correction unit 76 of FIG. 7, and FIG. 9E is an example of an output signal of the reference blood glucose concentration correction unit 76 of FIG. 7 .

The correction model generation unit 78 performs a PLS process on the output signal of the reference blood glucose concentration correction unit 76 and the optical signal that has undergone the preprocessing or has not undergone the preprocessing, do. The PLS processing is well known in the technical field to which the present invention belongs, and a detailed description thereof will be omitted. FIG. 9F is an example of an output signal of the correction model generation unit 78 of FIG.

The blood glucose concentration estimating unit 66 of FIG. 6 receives the calibration model received from the calibration model establishing unit 70 and an optical signal that has undergone the preprocessing or has not undergone the preprocessing, and estimates the blood glucose concentration Function, and performs PLS processing at this time. FIG. 9G is an example of an output signal of the blood glucose concentration estimating unit 66 of FIG. With respect to the estimated blood glucose concentration, the blood glucose concentration correction unit 68 performs a function of correcting the blood glucose concentration by dividing by the area of the AC portion of the PPG signal to output an accurate blood glucose concentration. FIG. 9H is an example of an output signal of the blood glucose concentration correction unit 68 of FIG.

Hereinafter, with reference to FIG. 8, the method for correcting blood sugar concentration of the present invention will be described. FIG. 8 is a flowchart of a second embodiment for explaining the method of correcting blood glucose concentration according to the present invention. Examples of output signals at each step are shown in Figs. 9A to 9H.

As shown in the figure, the method of the present invention receives an optical signal measured in the bloodless blood sugar system as shown in FIG. 1 (S81), and receives a reference blood glucose concentration which is a concentration at the time when the optical signal is measured (S83 ). S81 and S83 do not describe the time-series order, but can be executed sequentially (independently of the order) or independently of each other. The reference blood glucose concentration is the concentration of blood glucose directly measured by blood collection as described above. Then, the PPG signal measuring unit 62 measures the PPG signal of the blood vessel of the patient (S85). As described above, the PPG signal measuring unit 62 may be a pulse oximeter, and a detailed description of the operation of the pulse oximeter will be omitted.

In addition, the method of the present invention performs preprocessing using any one of a method of performing background removal using polynomial fitting for the received optical signal, a PCA method, an ICA method, and an NMF method (S87). The above method is described above. However, although S87 has been described after S85 for the sake of convenience, it may be performed before S85, and it may be that the preprocessing of S87 may not be performed as described above.

Thereafter, the method of the present invention estimates the blood glucose concentration using the correction model generated using the reference blood glucose concentration (S89). In the estimation of the blood glucose concentration using the correction model in S89, the generation of the correction model is performed by performing the preprocessing by measuring the PPG signal and the received optical signal in the same manner as S87, The correction is performed by multiplying the concentration by the area of the AC portion of the PPG signal. The corrected blood glucose concentration thus generated and the optical signal for which the pre-processing is performed or the pre-processing is not performed are subjected to the PLS processing to generate the correction model. In addition, the blood glucose concentration estimation in S89 refers to a correction model and PLS processing for an optical signal that has undergone the preprocessing or has not undergone the preprocessing.

Thereafter, the estimated blood glucose concentration is divided by the area of the AC portion of the PPG signal to correct the blood glucose concentration, thereby outputting an accurate blood glucose concentration.

According to the blood glucose concentration correcting apparatus and method of the present invention, accurate blood glucose concentration can be obtained by correcting the blood glucose concentration in consideration of the volume change of blood vessels in bloodless blood glucose measurement.

12, 22, 62, 72: PPG signal measuring unit 14, 24, 64, 74:
16, 26: optical signal correcting unit 18: blood glucose concentration correcting unit
20, 70: correction model establishing unit 28, 78:
66: blood glucose concentration estimating unit 68: blood glucose concentration correcting unit
76: reference blood glucose concentration correction unit

Claims (10)

A method for correcting a blood sugar concentration of an optical signal obtained by irradiating light on a predetermined body part of a patient using a PPG signal of a blood vessel of a patient and an actually measured reference blood glucose concentration of the patient, In the apparatus,
A first correcting unit for performing a correction for dividing the optical signal by an area of a portion where the change of the PPG signal exists (AC portion);
A setup unit for establishing a calibration model for blood glucose concentration using the reference blood glucose concentration; And
And a second correction unit for performing a partial least squares (PLS) process on the correction model established by the setting unit and the optical signal corrected by the first correction unit to perform correction of blood glucose concentration.
The method of claim 1, wherein the optical signal is one of a background removal method using a polynomial fitting, a principal component analysis (PCA) method, an independent component analysis (ICA) method, and a non-numerical factor factorization (NMF) And a preprocessing unit for performing preprocessing.
3. The apparatus according to claim 1 or 2,
A third corrector for performing a correction for dividing the optical signal by the area of the AC portion of the PPG signal; And
And a generation unit for performing a PLS process on the reference blood glucose concentration and the optical signal corrected by the third correction unit to generate a correction model.
4. The apparatus of claim 3, wherein the configuration unit further comprises a preprocessing unit for performing preprocessing on the optical signal using any one of a background removal method using polynomial fitting, a PCA method, an ICA method, and an NMF method. Device.
A correction unit for receiving a PPG signal of a blood vessel of a patient, an actually measured reference blood glucose concentration of the patient, and an optical signal obtained by irradiating light to a predetermined body part of the patient to correct the blood glucose concentration of the optical signal, In the method,
Performing a correction to divide the optical signal by the area of the AC portion of the PPG signal;
A step of PLS-processing a signal obtained by performing a correction for dividing the reference blood glucose concentration and the optical signal by the area of the AC portion of the PPG signal to establish a correction model for blood glucose concentration; And
Performing PLS processing on the correction signal and the optical signal on which the correction has been performed to thereby perform correction of blood glucose concentration.
A correction device for correcting a blood glucose concentration of an optical signal obtained by irradiating a predetermined body part of a patient with a PPG signal of a patient's blood vessel and an actually measured reference blood glucose concentration of the patient,
A setup unit for establishing a calibration model for blood glucose concentration using the reference blood glucose concentration;
An estimating unit for estimating blood glucose concentration by PLS processing the optical signal and the correction model established by the establishing unit; And
And a first correction section for performing correction for dividing the blood glucose concentration estimated by the estimation section and the area of the AC section of the PPG signal.
The apparatus of claim 6, further comprising a preprocessor for performing preprocessing on the optical signal using any one of a background removal method using polynomial fitting, a PCA method, an ICA method, and an NMF method.
8. The image processing apparatus according to claim 6 or 7,
A second corrector for performing a correction on the reference blood glucose concentration by multiplying the reference blood glucose concentration by an area of an AC portion of the PPG signal; And
And a generation unit for PLS-processing the output signal of the second correction unit and the optical signal to generate a correction model.
9. The apparatus of claim 8, wherein the configuration unit further comprises a preprocessing unit for performing preprocessing on the optical signal using any one of a background removal method using polynomial fitting, a PCA method, an ICA method, and an NMF method. Device.
A correction unit for receiving a PPG signal of a blood vessel of a patient, an actually measured reference blood glucose concentration of the patient, and an optical signal obtained by irradiating light to a predetermined body part of the patient to correct the blood glucose concentration of the optical signal, In the method,
Performing a PLS processing on a signal obtained by performing a correction for multiplying the reference blood glucose concentration by an area of an AC portion of the PPG signal and the optical signal to establish a correction model for blood glucose concentration;
Performing PLS on the optical signal and the correction model to estimate blood glucose concentration; And
Dividing the estimated blood glucose concentration by the area of the AC portion of the PPG signal to perform correction of blood glucose concentration.

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