Patent Application
20230317218
The present invention relates to a uric acid level estimation device, a uric acid level estimation method, and a computer program.
Conventionally, it has been common to collect blood of a subject and perform biochemical analysis to measure the uric acid level. However, in this method, a needle or the like needs to be invasively inserted into the skin of the subject, which causes a psychological or physical burden on the subject. For example, a method disclosed in Patent Literature 1 has been known as a method of non-invasively estimating uric acid. In the method disclosed in Patent Literature 1, uric acid is extracted from a biological specimen such as a nail clipping, hair, or skin.
Patent Literature 1
Japanese Patent Laid-Open No. 2008-203067
Psychology Research and Behavior Management 2011:4 81-86, Summary of the clinical investigations E. S. Teck Complex Mar. 20, 2010 Overview
R. N. Chua, Y. W. Hau, C. M. Tiew and W. L. Hau, “Investigation of Attention Deficit/Hyperactivity Disorder Assessment Using Electro Interstitial Scan Based on Chronoamperometry Technique”, in IEEE Access, vol. 7, pp. 144679-144690, 2019, doi: 10.1109/ACCESS.2019.2938095.
Maarek A., Electro interstitial scan system: assessment of 10 years of research and development. Med Devices (Auckl). 2012;5:23-30. doi:10.2147/MDER.S29319
However, since it is needed to collect a tissue sample such as a nail clipping, hair, or skin from a subject and perform an extraction process, it has been difficult to easily and swiftly measure the uric acid level at a health checkup or the like.
The present invention is made in view of the above-described situation and is intended to provide a uric acid level estimation device, a uric acid level estimation method, and a computer program that are capable of extremely accurately estimating uric acid based on non-invasive biological information.
A uric acid level estimation device according to the present invention includes an information acquisition unit configured to acquire attribute information and non-invasive biological information of a predetermined user, an estimation model storage unit configured to store a uric acid level estimation model, and an estimation processing unit configured to calculate a uric acid level estimated value of the predetermined user based on the attribute information and/or non-invasive biological information of the predetermined user by using the uric acid level estimation model.
The uric acid level estimation device according to the present invention further includes a training data storage unit configured to store a training data set, and a learning processing unit configured to generate the uric acid level estimation model by machine learning based on the training data set.
The attribute information includes any one or a combination of age and sex, and the non-invasive biological information includes any one or a combination of BMI, blood pressure, pulse wave data, electrocardiogram data, and biological impedance.
The training data set includes attribute information, non-invasive biological information, and a blood-measured uric acid measured value of a subject.
The non-invasive biological information further includes oxygen saturation (SpO2).
The estimation accuracy of the uric acid estimated value is such that the coefficient of correlation between the estimated uric acid and the actual uric acid is equal to or larger than 0.6.
The estimation processing unit calculates a uric acid level risk estimated value in place of the uric acid level estimated value.
The learning processing unit provides labels indicating existence of the uric acid level risk to the training data set based on the blood-measured uric acid measured value, and when a difference between the numbers of pieces of data with the uric acid level risk and data without the uric acid level risk among the labels is equal to or larger than a predetermined value, the learning processing unit increases the number of pieces of sample data in the training data set to reduce the difference.
The learning processing unit generates a first uric acid level risk estimation model and a second uric acid level risk estimation model by machine learning based on each of training data sets of different kinds, and the estimation processing unit calculates the uric acid level risk estimated value of the predetermined user by using the first uric acid level risk estimation model and the second uric acid level risk estimation model.
The uric acid level estimation device according to the present invention further includes a biological information estimation unit configured to estimate at least one piece or more of biological information among BMI, blood pressure, pulse wave data, electrocardiogram data, biological impedance, and oxygen saturation included in the biological information, and the information acquisition unit acquires, as biological information of the predetermined user, the biological information estimated by the biological information estimation unit.
A non-invasive uric acid level estimation system includes the uric acid level estimation device, and a biological information measurement device configured to measure non-invasive biological information.
A uric acid level estimation method according to the present invention includes a step of storing a training data set including attribute information, non-invasive biological information, and a blood-measured uric acid measured value of a subject, a step of generating the uric acid level estimation model by machine learning based on the training data set, and a step of calculating a uric acid level estimated value of the predetermined user based on the attribute information and/or non-invasive biological information of the predetermined user by using the uric acid level estimation model.
A computer program according to the present invention causes a computer to execute a step of storing a training data set including attribute information, non-invasive biological information, and a blood-measured uric acid measured value of a subject, a step of generating the uric acid level estimation model by machine learning based on the training data set, and a step of calculating a uric acid level estimated value of the predetermined user based on the attribute information and/or non-invasive biological information of the predetermined user by using the uric acid level estimation model.
According to the present invention, it is possible to provide a uric acid level estimation device, a uric acid level estimation method, and a computer program that are capable of extremely accurately estimating uric acid, in other words, a health risk of uric acid by machine learning by using non-invasive biological information.
An embodiment will be described below with reference to the accompanying drawings. Note that the embodiment is exemplary and the present invention is not limited to configurations described below.
A uric acid level estimation system 1 and a uric acid level estimation device 30 according to the present embodiment will be described below with reference to
A “user” is a person who uses the uric acid level estimation system to non-invasively obtain an estimated value of the uric acid level. A “subject” is a person who provides, upon a predetermined procedure and an agreement, attribute information such as age or sex, non-invasive biological information, and a blood-measured uric acid measured value as a training data set to be used in the uric acid level estimation system.
The terminal device 10 may be any information terminal to which the attribute information (such as full name, ID, age, or sex) of the user can be input and that can output the input information to the uric acid level estimation device 30 through a wired or wireless communication network. Examples of the terminal device 10 include portable terminals including a tablet terminal, a smartphone, and a wearable terminal, and include a personal computer (PC). Note that, height, weight, or the like may be measured by the biological information measurement device 20 to be described later.
The biological information measurement device 20 measures the non-invasive biological information of the user. The non-invasive biological information is biological information acquired by a method that does not require insertion of an instrument into the skin or an opening part of the body. The non-invasive biological information may be measured by using, for example, a commercially available height meter, weight meter, blood pressure meter, pulse oximeter, pulse wave meter, electrocardiogram meter, impedance measurement machine, or galvanic skin measurement machine. Alternatively, ES-TECK BC-3 (Ryobi Systems Co., Ltd.) that can simultaneously measure pulse wave data, electrocardiogram data, biological impedance, and oxygen saturation (SpO2) may be used. These devices can measure non-invasive biological data without providing a psychological nor physical load on the user.
In the embodiment of the present invention, the non-invasive biological information includes any one or a combination of the body mass index (BMI), blood pressure, pulse wave data, electrocardiogram data, and biological impedance and may further include oxygen saturation (SpO2).
The BMI is calculated by the following formula based on a height h [m] and a weight w [kg].
BMI=w/h2 [kg/m2]
The circulating blood amount is calculated by the following Nadler formula.
<Male> Circulating blood amount [L]=0.3669×h3+0.03129×w+0.6041
<Female> Circulating blood amount [L]=0.3561×h3+0.03308×w+0.1833
The blood pressure includes any one or a combination of systolic blood pressure, diastolic blood pressure, pulse pressure, and average arterial blood pressure.
The pulse pressure is calculated by the following expression.
Pulse pressure=systolic blood pressure−diastolic blood pressure
The average arterial blood pressure is calculated by the following expression.
Average arterial blood pressure=diastolic blood pressure+pulse pressure×⅓
The pulse wave data is measured by irradiating, by using a sphygmograph or a pulse oximeter, a protruding body site such as a finger with red light (up to 660 nm) from a red LED and with near-infrared light (up to 905 nm) from an IR LED and measuring transmitted light thereof by using a phototransistor.
The pulse wave data includes any one or a combination of pulse, the elasticity index, the peripheral vascular resistance, the acceleration plethysmogram, b/a, e/a,-d/a, the Takazawa's second derivative of photoplethysmogram aging index, the ejection fraction, the LVET, and the dicrotic elasticity index (DEI).
The elasticity index is a numerical value obtained by dividing the height by the time from detection of a systolic peak to detection of a diastolic peak in the photoplethysmogram. The peripheral vascular resistance is calculated by “average arterial blood pressure”/“cardiac output”×80. The dicrotic elasticity index (DEI) is an indicator of the diastolic vascular elasticity and can be measured by a PWV measurement device. The DEI of 0.3 to 0.7 is normal, the DEI of 0.3 or lower indicates the possibility of high-blood pressure or arteriosclerosis, and the DEI of 0.7 or higher indicates the possibility of acute anxiety neurosis.
The acceleration plethysmogram is the second derivative of photoplethysmogram (PTG) (SDPTG). The acceleration plethysmogram is constituted by the initial positive wave (a wave), the initial negative wave (b wave), the mesosystolic re-elevation wave (c wave), the late systolic re-descent wave (d wave), and the early diastolic positive wave (e wave), and b/a, e/a, and-d/a described above are calculated from ratios of the heights of the waves. It is observed that b/a increases and c/a, d/a, and e/a decrease along with aging, and thus aging of blood vessels can be evaluated by the Takazawa's second derivative of photoplethysmogram aging index (b-c-d-e)/a. The ejection fraction is the ratio of blood transferred from the ventricles at each heartbeat and is proportional to the second derivative of photoplethysmogram aging index. The LVET is the left ventricular ejection time in which blood in the left ventricle is ejected to the aorta after the aortic valve is opened.
The electrocardiogram data can be measured by electrocardiography (ECG) with electrodes or by photoplethysmography (PPG).
The electrocardiogram data includes any one or a combination of the breathing rate, the heart rate, the RR interval, the standard deviation of the RR interval, the MxDMn ratio, the power spectrum in a low frequency band, the power spectrum in a high frequency band, the heart rate variation indicator LF/HF, and the total power. The RR interval is the interval from a QRS wave to the next QRS wave in the electrocardiogram. The MxDMn ratio is the ratio of the longest RR interval and the shortest RR interval in a time period and is an index of irregular heartbeats. The total power is a calculated value of the total power of the power spectrum at the frequency of 0 to 0.4 Hz (VLF, LF, HF) in a measurement of two minutes. This value reflects the entire autonomic nerve activity dominated by sympathetic nerve activity.
The high-frequency power spectrum ratio (0.1875 to 0.50 Hz; HF), the low-frequency power spectrum ratio (0.05 to 0.1875 Hz; LF), the LF/HF ratio, and the very-low-frequency power spectrum ratio (0 to 0.05 Hz; VLF) can be calculated by calculating the power spectrum density based on the electrocardiogram.
The biological impedance (conductance) can be measured by, for example, generating small current flow between two electrodes among electrodes at the six sites of the legs, the hands, and the right and left foreheads. When current flows between two of the electrodes at the six sites, (1) anode/cathode conductance (μS), (2) cathode/anode conductance (μS), (3) the difference (delta SCRA-SCRC) between the conductance measured in (1) above and the conductance measured in (2) above, and (4) electric conductivity (μS/m) can be measured. In addition, the muscle mass, the body fat amount, the total moisture content, the phase angle, and the resistance value can be simultaneously measured. In addition, the dielectric constant (μSi) can be measured for cases of conduction between the right hand and the left hand and between the right forehead and the left forehead. The biological impedance (conductance) is preferably measured by using 22 conduction patterns with the electrodes at the six sites.
The biological impedance includes any one or a combination of the body fat amount (kg), the body fat amount (%), the lean body weight, the lean body rate, the muscle mass, the total moisture content (kg), the total moisture content (%), the in-cell moisture content (%), the cardiac output, 1 forehead left-side-2 left hand/SCR A, 1 forehead left-side-2 left hand/delta SCR C-SCR A, 5 left hand-6 left foot/delta SCR C-SCR A, 13 left foot-14 right foot/SCR C, 13 left foot-14 right foot/SCR A, 15 right hand-16 forehead left-side/delta SCR C-SCR A, 15 right hand-16 forehead left-side SCR C, 19 right foot-20 left hand/delta SCR C-SCR A, ESG 2+4+15+17 (μS/m), ESG 6+13+19 (%), ESG 6+8+19+21 (%), ESG 6+8+19+21 (μS/m), ESG 9+10 (μS/m), ESG 9+10 (%), the left-foot conductance, R (Ω), the phase angle, the dielectric constant through a forehead path, forehead-path electric conductivity (9), the dielectric constant through a hand-to-hand path, hand-to-hand electric conductivity (11, 12), the single-output amount (cardiac output/heart rate), and the circulating blood coefficient (cardiac output×circulating blood amount).
SCR stands for skin conductance response, and ESG stands for electroscangram. The symbol “+” in ESG 2+4+15+17 indicates electrodes attached to the body and used for measurement. For example, ESG 2+4+15+17 means the average of conductance values measured at the left hand when conduction is made from the left hand to the left forehead, the right hand when conduction is made from the right hand to the right forehead, the right hand when conduction is made from the right hand to the left forehead, and the left hand when conduction is made from the left hand to the right forehead as illustrated in
The value “1 forehead left-side-2 left hand/SCR A” is conductance (or conductivity) measured through a path when current flows with “1 forehead left-side” at the cathode and “2 left hand” at the anode, and the value “5 left hand-6 left foot/delta SCR C-SCR A” is the difference between conductance values measured when conduction is made with “5 left hand” and “6 left foot” at the anode and the cathode and at the cathode and the anode.
The BMI and the blood pressure can be measured by a height-weight meter and a blood pressure meter. The non-invasive biological information may include an oxygen transport amount calculated based on SpO2 and the cardiac output.
The measured non-invasive biological information is output to the uric acid level estimation device 30 through a wired or wireless communication network. The biological information measurement device 20 may be a fixed measurement device or a portable measurement device such as a wearable terminal.
The uric acid level estimation device 30 includes a first acquisition unit 31, a second acquisition unit 32, a user data storage unit 33, a training data storage unit 34, a learning processing unit 35, an estimation model storage unit 36, an estimation processing unit 37, and an estimation data storage unit 38. The first acquisition unit 31 acquires the attribute information of the user from the terminal device 10. The second acquisition unit 32 acquires the non-invasive biological information of the user from the biological information measurement device 20.
The user data storage unit 33 stores the attribute information and the non-invasive biological information of the user, which are acquired from the first acquisition unit 31 and the second acquisition unit 32.
The training data storage unit 34 stores, as training data sets for machine learning, a plurality of training data sets each consisting of the attribute information and the non-invasive biological information of a plurality of subjects, which are acquired in advance and sample examination information, such as the uric acid level, which is obtained through a blood examination. Note that the sample examination information may further include examination information obtained from blood, urine, stool, or the like.
The learning processing unit 35 acquires the training data sets stored in the training data storage unit 34 and produces a uric acid level estimation model by using the training data sets. Specifically, the acquired training data sets are normalized, and the relation among the attribute information, the non-invasive biological information, and the uric acid is learned by machine learning by a neural network (NN), gradient boosting such as XGBoost, linear regression, or the like.
The estimation model storage unit 36 stores the uric acid level estimation model generated by the learning processing unit 35.
The non-invasive biological information includes any one or a combination of the BMI, the blood pressure, the pulse wave data, the electrocardiogram data, and the biological impedance. In addition, the oxygen saturation (SpO2) is included as necessary.
The estimation processing unit 37 estimates the uric acid level of the predetermined user based on the attribute information and/or the non-invasive biological information of the user by using the estimation model generated by the learning processing unit 35. Then, the uric acid level estimated value is stored in the estimation data storage unit 38.
The display device 39 can display the uric acid level estimated value together with the attribute information and the non-invasive biological information of the user. Note that these pieces of data may be displayed on the terminal device 10 possessed by the user.
Note that the first acquisition unit 31, the second acquisition unit 32, the learning processing unit 35, the estimation processing unit 37, and the like described above function at the processors 301 of the uric acid level estimation device 30 when operating.
It is possible to perform uric acid estimation without performing blood examination, by generating a uric acid level estimation model by machine learning based on non-invasive biological data including the body mass index (BMI), the blood pressure, the pulse wave data, the electrocardiogram data, the biological impedance, and the like.
As described below, it is also possible to determine whether the uric acid is normal even when the number of pieces of data included in the non-invasive biological data is limited.
At step ST101, the learning processing unit 35 performs preprocessing of input data. Specifically, the learning processing unit 35 converts attribute information of sex of each subject into a One-hot vector. In addition, the learning processing unit 35 normalizes attribute information other than sex, the non-invasive biological information of each subject, and uric acid sample examination information obtained through a blood examination through yeo-johnson transformation, boc-box transformation, and the like.
At step ST102, the learning processing unit 35 performs machine learning by a neural network (NN).
As illustrated in
The learning processing unit 35 stores the uric acid level estimation model generated by the above-described learning processing in the estimation model storage unit 36.
Note that the above-described machine learning algorithm is exemplary and the present invention is not limited thereto.
At step ST201, the first acquisition unit 31 of the uric acid level estimation device 30 acquires the attribute information of the user from the terminal device 10. At step ST202, the second acquisition unit 32 of uric acid level estimation device 30 acquires the non-invasive biological information of the user. Then, the attribute information and the non-invasive biological information of the user are stored in the user data storage unit 33. Then at step ST203, the estimation processing unit 37 calculates a uric acid level estimated value by using the uric acid level estimation model stored in the estimation model storage unit 36.
At step ST204, the calculated uric acid level estimated value is stored in the estimation data storage unit 38. At step ST205, the uric acid level estimated value is output to an external terminal such as the display device 39 and displayed.
Examples of the present application invention will be described below. However, the present invention is not limited to the examples below.
The attribute information includes ID, full name, age, and sex, and the non-invasive biological information includes the BMI, the blood pressure, the pulse wave data, the electrocardiogram data, the biological impedance, and the oxygen saturation (SpO2). Height and weight as calculation references of the BMI were measured by a height meter and a weight meter, respectively, and the blood pressure was measured by a blood pressure meter. The pulse wave data, the electrocardiogram data, the biological impedance, and the oxygen saturation (SpO2) were measured by ES-TECK BC-3 (Ryobi Systems Co., Ltd.). Note that a pulse wave meter, an electrocardiogram meter, an impedance measurement device, and a pulse oximeter that are commercially available may be used in combination in place of ES-TECK BC-3. The above-described non-invasive biological information may be acquired by using a predetermined wearable terminal.
The biological impedance (conductance) was measured by generating small current flow between two electrodes among electrodes at the six sites of the legs, the hands, and the right and left foreheads. Voltage and current were 1.28 V and 200 μA, respectively, and the conductance was measured for 32 milliseconds per second. Current was caused to flow between two of the electrodes at the six sites to measure (1) anode/cathode conductance (μS), (2) cathode/anode conductance (μS), (3) the difference (delta SCRA-SCRC) between the conductance measured in (1) above and the conductance measured in (2) above, and (4) electric conductivity (μS/m).
In addition, the muscle mass, the body fat amount, the total moisture content, the phase angle, and the resistance value were measured, and the dielectric constant (μSi) was measured for cases of conduction between the right hand and the left hand and between the right forehead and the left forehead.
The pulse wave data, the electrocardiogram data, the biological impedance, and the oxygen saturation (SpO2) were measured for two minutes by using ES-TECK BC-3 for each subject. At the measurement, a device having functions of an electrocardiogram, a pulse wave meter, and a pulse oximeter was mounted on the left hand forefinger of each subject, two electrodes were mounted on the forehead, and the hands and feet were placed on electrode plates while the subject was seated on a chair.
With a learning model 1, machine learning by a neural network (NN) was performed as illustrated in
In this case, data described below was selected and used as the attribute information and non-invasive biological data. (A) the attribute information: sex, (B) the non-invasive biological data: the BMI, the circulating blood amount, the blood pressure, the average arterial blood pressure, the systolic blood pressure, the diastolic blood pressure, the pulse pressure, the pulse wave data, the peripheral vascular resistance, pulse, the biological impedance, the lean body weight (kg), the total moisture content (kg), the cardiac output, R (Ω), the dielectric constant through a forehead path, the dielectric constant through a hand-to-hand path, the electrocardiogram data, and the heart rate.
The non-invasive biological data also includes the single-output amount obtained by dividing the cardiac output by the heart rate, pulse pressure and pulse data, and the circulating blood coefficient calculated based on the circulating blood amount and the single-output amount.
In Example 1, a uric acid level estimation model was generated through machine learning of the above-described learning model 1 by using (1) the attribute information, (2) the non-invasive biological information measured by a height-weight meter, a blood pressure meter, and ES-TECK BC-3, and (3) a training data set of uric acid obtained through a blood examination performed on the same day as the non-invasive biological information measurement for a total of 712 subjects.
Then, the estimation accuracy of the uric acid level estimation model was determined by calculating the coefficient of correlation with actually measured uric acid. As a result, the average, standard deviation, and standard error of error between the uric acid level estimated value and the actual uric acid were 0.14, 1.05, and 0.08, respectively. The coefficient of correlation between the actual uric acid value and the predicted uric acid was 0.63. A test of no correlation obtained a p value less than 0.001, and thus correlation exists between the uric acid level estimated by the estimation model and the uric acid level obtained through a blood examination. As described above, it is possible to estimate the uric acid without performing a blood examination, by generating a uric acid level estimation model by machine learning based on the non-invasive biological data including the body mass index (BMI), the blood pressure, the pulse wave data, the electrocardiogram data, and the biological impedance.
As described below, it is possible to determine “uric acid level risk”, in other words, whether the uric acid level is normal even when the number of pieces of data included in the non-invasive biological data is limited.
At step ST301, the learning processing unit 35 performs preprocessing of input data. Specifically, for uric acid obtained through a blood examination, the learning processing unit 35 converts the uric acid lower than 7.0 mg/dL into “0” (no risk is present) and the uric acid equal to or higher than 7.0 mg/dL into “1” (risk is present). When the number of subjects classified as “0” and the number of subjects classified as “1” are deviated and unbalanced, the learning processing unit 35 may apply SMOTE (Chawla, NV. et al. 2002) to learning data to artificially generate training samples. Specifically, a label (for example, above-described “0” or “1”) indicating existence of the uric acid level risk may be provided to each input data (training data set) based on the measured value of uric acid obtained through a blood examination. Then, when the difference between the number of labels with the uric acid level risk (label “1”) and the number of labels without the uric acid level risk (label “0”) is equal to or larger than a predetermined value, the number of pieces of sample data in the training data set may be increased (generated) to reduce the difference.
At step ST302, the learning processing unit 35 performs machine learning by logistic regression or random forest.
For example, Logistic Regression provided in a Python open-source machine learning library Scikit-learn may be used for the machine learning by logistic regression. The number of dimensions may be reduced by primary component analysis as necessary. The uric acid level risk obtained through a blood examination was compared with the uric acid level risk estimated by machine learning, and parameters (C, regularization method, max_iter, and solber) of Logistic Regression were adjusted to obtain the maximum f1 score. The parameter “C” is a tradeoff parameter that determines the strength of regularization, and the strength of regularization is weaker as the value of the parameter is larger. The parameter “regularization method” means L1 regularization or L2 regularization to be selected. The parameter “max_iter” is the maximum number of iterations of learning. The parameter “solber” selects a convergence method (for example, the L-BFGS method, the Newton CG method, liblinear, sag, or saga) that minimizes the cross-entropy loss. Note that the liblinear method was selected in Examples 2 and 3 below.
For example, Random Forest Classifier provided in a Python open-source machine learning library Scikit-learn may be used for the machine learning by random forest. The uric acid level risk obtained through a blood examination was compared with the uric acid level risk estimated by machine learning, and parameters (max_depth, max_features, and n_estimators) of Random Forest Classifier were adjusted to obtain the maximum f1 score. The parameter “max_depth” is the depth of a decision tree, and the parameter “max_features” designates the randomness of each tree. The parameter “n_estimators” is the number of decision trees to be established. However, max_depth was None or 1 to 7, subsample was 0.3 to 0.7, max_features was optimally selected from among “auto”, “sqrt”, and “log”, and n_estimators was adjusted in the range of 10 to 1000.
The learning processing unit 35 stores the uric acid level risk estimation model generated by the above-described learning processing in the estimation model storage unit 36.
Note that the above-described machine learning algorithm is exemplary and the present invention is not limited thereto.
As illustrated in
Examples of uric acid level risk estimation will be described below. However, aspects of the uric acid level risk estimation in the present invention are not limited to the examples below.
The attribute information includes any one or a combination of ID, full name, age, and sex, and the non-invasive biological information includes any one or a combination of the BMI, the blood pressure, the pulse wave data, the electrocardiogram data, the biological impedance, and the oxygen saturation (SpO2). Height and weight as calculation references of the BMI were measured by a height meter and a weight meter, respectively, and the blood pressure was measured by a blood pressure meter. The pulse wave data, the electrocardiogram data, the biological impedance, and the oxygen saturation (SpO2) were measured by ES-TECK BC-3 (Ryobi Systems Co., Ltd.). Note that a pulse wave meter, an electrocardiogram meter, an impedance measurement device, and a pulse oximeter that are commercially available may be used in combination in place of ES-TECK BC-3. The above-described non-invasive biological information may be acquired by using a predetermined wearable terminal.
The biological impedance (conductance) was measured by generating small current flow between two electrodes among electrodes at the six sites of the feet, the hands, and the right and left foreheads. Voltage and current were 1.28 V and 200 μA, respectively, and the conductance was measured for 32 milliseconds per second. Current was caused to flow between two of the electrodes at the six sites to measure (1) anode/cathode conductance (μS), (2) cathode/anode conductance (μS), (3) the difference (delta SCRA-SCRC) between the conductance measured in (1) above and the conductance measured in (2) above, and (4) electric conductivity (μS/m).
In addition, the muscle mass, the body fat amount, the total moisture content, the phase angle, and the resistance value were measured, and the dielectric constant (μSi) was measured for cases of conduction between the right hand and the left hand and between the right forehead and the left forehead.
The pulse wave data, the electrocardiogram data, the biological impedance, and the oxygen saturation (SpO2) were measured for two minutes by using ES-TECK BC-3 for each subject. At the measurement, a device having functions of an electrocardiogram, a pulse wave meter, and a pulse oximeter was mounted on the left hand forefinger of each subject, two electrodes were mounted on the forehead, and the hands and feet were placed on electrode plates while the subject was seated on a chair.
With a learning model 2, machine learning by random forest was performed as illustrated in
With a learning model 3, machine learning by logistic regression was performed as illustrated in
The non-invasive biological data also includes the pulse pressure and pulse data, the circulating blood amount, and the circulating blood coefficient calculated based on the single-output amount.
In Example 2, the uric acid level risk estimation model was generated through machine learning of the above-described learning model 2 by using (1) the attribute information, (2) the non-invasive biological information measured by a height-weight meter, a blood pressure meter, and ES-TECK BC-3, and (3) a training data set of uric acid obtained through a blood examination performed on the same day as the non-invasive biological information measurement for 321 subjects.
Then, an estimation result was evaluated by using an ROC_AUC curve for the estimation accuracy of the uric acid level risk estimation model. As a result, ROC_AUC was 0.81, which exceeds 0.8 indicating extremely favorable classification. The ROC_AUC curve of the estimation result in Example 2 is illustrated in
In Example 3, the uric acid level risk estimation model was generated through machine learning of the above-described learning model 3 by using (1) attribute information, (2) the non-invasive biological information measured by a height-weight meter, a blood pressure meter, and ES-TECK BC-3, and (3) a training data set of uric acid obtained through a blood examination performed on the same day as the non-invasive biological information measurement for a total of 712 subjects.
Then, an estimation result was evaluated by using an ROC_AUC curve for the estimation accuracy of the uric acid level risk estimation model. As a result, ROC_AUC was 0.75, which exceeds 0.7 indicating favorable classification. The ROC_AUC curve of the estimation result in Example 3 is illustrated in
In the above-described embodiment, the uric acid level risk is estimated by using the learning model 2 or the learning model 3, but the uric acid level risk may be estimated by using a plurality of learning models.
Accordingly, the uric acid level risk can be estimated at higher accuracy than the uric acid level risk is estimated by using one learning model.
In the above-described embodiment and examples, the estimation accuracy improves in some cases when the BMI is used for a learning model data set, and thus a functional component configured to estimate the BMI may be provided in a uric acid level risk estimation device.
The BMI is typically not acquired by a wearable terminal nor the like but is calculated based on a height and a weight input by the user. However, when the BMI is estimated, the above-described uric acid level risk can be acquired by only acquiring biological information, which improves convenience for the user.
The BMI estimation is not limited to a particular method, but for example, it is known that the BMI is correlated with inclination of the abdominal region (predetermined position) of the user. Thus, for example, a predetermined acceleration sensor may be provided on the abdominal region of the user (or a wrist-band wearable terminal or the like including an acceleration sensor may be placed on the abdominal region), and the BMI may be estimated by calculating the inclination of the abdominal region based on data output from the acceleration sensor.
Similarly to the above description, the pulse wave data or the oxygen saturation may be estimated by using a wrist-band wearable terminal or the like including a pulse wave sensor or a blood oxygen level sensor.
Similarly to the above description, the blood pressure may be estimated by using a wrist-band wearable terminal or the like. Since it is known that the blood pressure is correlated with the speed of a pulse wave transferred through an artery by heartbeat, the blood pressure may be estimated by using a predetermined sensor configured to measure the speed of a pulse wave transferred through an artery by heartbeat.
Similarly to the above description, the electrocardiogram data may be estimated by using a wrist-band wearable terminal or the like. For example, the electrocardiogram data may be estimated based on data obtained from an electrode provided on a surface on a side opposite a display surface of a wrist-band wearable terminal and an electrode provided on the display surface side. Specifically, the electrocardiogram data may be estimated based on data obtained when the wrist of a hand (for example, the left hand) on which the wrist-band wearable terminal is mounted contacts the electrode provided on the opposite surface and a fingertip of a hand (for example, the right hand) opposite to the mounted hand contacts the electrode provided on the display surface side.
Similarly to the above description, the biological impedance may be estimated by using a wrist-band wearable terminal or the like including various electrodes. For example, the biological impedance may be estimated based on biological information obtained from the thoracic region and a wrist by using a wrist-band wearable terminal or the like.
Note that the above-described estimation target biological information (at least one piece or more of biological information among the BMI, the blood pressure, the pulse wave data, the electrocardiogram data, the biological impedance, and the oxygen saturation) may be estimated by using a classifier generated by using various kinds of machine learning algorithms with, as teacher data, biological information that is acquirable by a wearable terminal and the above-described estimation target biological information.
In this case, the above-described second acquisition unit may acquire the estimated biological information.
For example, the series of above-described processing may be executed by hardware or software. In other words, the above-described functional configurations are merely exemplary and not particularly limited. Specifically, it suffices that the functionality of executing the entire series of above-described processing is provided at an information processing system, and which functional blocks are used to achieve the functionality is not particularly limited to the above-described example. Places at which functional blocks exist are not particularly limited to those in
When the series of processing is executed by software, computer programs constituting the software are installed on a computer or the like from a network or a recording medium. The computer may be a computer incorporated in dedicated hardware. Alternatively, the computer may be a computer capable of executing various functions with various computer programs installed thereon, such as a server or a general-purpose smartphone or personal computer.
A recording medium including such computer programs is not only configured as a non-illustrated removable media distributed separately from the device body to provide the computer programs to a user or the like, but also configured as, for example, a recording medium incorporated in the device body in advance and provided to the user or the like. The computer programs can be distributed through a network, and thus the recording medium may be mounted on or accessible from a computer connected or connectable to the network.
Note that, in the present specification, steps representing the computer programs recorded in the recording medium include not only processing performed in a temporally sequential manner in accordance with an order but also processing not necessarily processed in a temporally sequential manner but executed in parallel or individually. In the present specification, system terms mean those of an overall device including a plurality of devices, a plurality of units, or the like.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2021-130176 | Aug 2021 | JP | national |
| 2022-040638 | Mar 2022 | JP | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/JP2022/015100 | 3/28/2022 | WO |
