Patent Application
20250079010
The present invention relates to a creatinine risk estimation device, a creatinine risk estimation method, and a computer program.
Creatinine is a metabolic product of creatinine phosphate, which is the source of energy supply to muscle. Typically, creatinine is discharged from muscle tissue to blood, filtrated through the glomerulus of the kidney, and then discharged into urine. Thus, the amount of creatinine in blood is utilized as an indicator for evaluation of the kidney function.
Conventionally, it has been necessary to collect blood of a subject and perform biochemical analysis to measure creatinine. 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.
Patent Literature 1 discloses a technology of non-invasively measuring the level of creatinine concentration in blood by a laser sensor system on-chip.
Japanese Translation of PCT International Application Publication No. 2020-520768
Psychology Research and Behavior Management 2011:4 81-86, Summary of the clinical investigations E. S. Teck Complex March 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, Patent Literature 1 discloses no specific method of measuring creatinine.
The present invention has been made in view of the above-described situation and is intended to provide a creatinine risk estimation device, a creatinine risk estimation method, and a computer program that are capable of extremely accurately and swiftly estimating creatinine risk on health based on non-invasive biological information without blood or urine collection.
A creatinine risk 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 creatinine risk estimation model, and an estimation processing unit configured to calculate a creatinine risk estimated value of the predetermined user based on the attribute information and/or the non-invasive biological information of the predetermined user by using the creatinine risk estimation model.
The creatinine risk 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 creatinine risk 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 creatinine measured value of a subject.
The non-invasive biological information further includes oxygen saturation (SpO2).
Estimation accuracy of the creatinine risk estimated value is accuracy at which risk existence can be classified with ROC_AUC of 0.7 or larger.
The learning processing unit provides labels indicating existence of the creatinine risk to the training data set based on the blood-measured creatinine measured value, and when a difference between the number of pieces of data with the creatinine risk and the number of pieces of data without the creatinine 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 creatinine risk estimation model and a second creatinine risk estimation model by machine learning based on each of training data sets of different kinds, and the estimation processing unit calculates the creatinine risk estimated value of the predetermined user by using the first creatinine risk estimation model and the second creatinine risk estimation model.
The creatinine risk 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 creatinine risk estimation system includes the creatinine risk estimation device, and a biological information measurement device configured to measure non-invasive biological information.
A creatinine risk 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 creatinine measured value of a subject, a step of generating a creatinine risk estimation model by machine learning based on the training data set, and a step of calculating a creatinine risk estimated value of a predetermined user based on the attribute information and/or the non-invasive biological information of the predetermined user by using the creatinine risk 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 creatinine measured value of a subject, a step of generating a creatinine risk estimation model by machine learning based on the training data set, and a step of calculating a creatinine risk estimated value of a predetermined user based on the attribute information and/or the non-invasive biological information of the predetermined user by using the creatinine risk estimation model.
According to the present invention, it is possible to provide a creatinine risk estimation device, a creatinine risk estimation method, and a computer program that are capable of extremely accurately estimating creatinine risk on health 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 creatinine risk estimation system 1 and a creatinine risk estimation device 30 according to the present embodiment will be described below with reference to
A “user” is a person who uses the creatinine risk estimation system to non-invasively obtain an estimated value of the creatinine risk. 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 creatinine measured value as a training data set to be used in the creatinine risk 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 creatinine risk 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 causing a psychological or physical burden 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 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×1/3
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, c/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 c/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−c)/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 electrocardiogramith 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 M×DMn 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 M×DMn 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 intercellular 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/SCR C, 5 left hand-6 left foot/delta SCR C-SCR A, 7 right hand-8 right foot/SCR C, 7 right hand-8 right foot/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, 15 right hand-16 forehead left-side SCR A, 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 (52), the phase angle, the forehead-path dielectric constant, the forehead-path electric conductivity (9), the one-hand-to-one-hand-path dielectric constant, the hand-to-hand electric conductivity (11, 12), the single-output amount (cardiac output/heart rate), the hand-foot impedance (sum value of 5 left hand-6 left foot/SCR C and 7 right hand-8 right foot/SCR).
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 “2left 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 creatinine risk 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 creatinine risk 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 creatinine, 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 creatinine risk estimation model by using the training data sets. Specifically, when the creatinine risk is estimated, the relation among the attribute information, the non-invasive biological information, and the creatinine risk is learned by machine learning with each acquired training data set by a neural network, logistic regression, or ensemble learning with results of the learning.
The estimation model storage unit 36 stores the creatinine risk 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 creatinine risk 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 creatinine risk estimated value is stored in the estimation data storage unit 38.
The display device 39 can display the creatinine risk 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 creatinine risk estimation device 30 when operating.
It is possible to perform creatinine estimation without performing blood examination, by generating a creatinine 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 creatinine 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, for creatinine obtained through a blood examination, the learning processing unit 35 converts the creatinine equal to or lower than 1.00 mg/dL into “0” (no risk is present) and the creatinine equal to or higher than 1.01 mg/dL into “1” (risk is present) in a case of male, and converts the creatinine equal to or lower than 0.70 mg/dL into “0” (no risk is present) and the creatinine equal to or higher than 0.71 mg/dL into “1” (risk is present) in a case of female. 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.
At step ST102, the learning processing unit 35 performs machine learning by the logistic regression and the neural network (NN). In
Compile A1, A2, and A3 each include a full connection layer “Linear” that performs full connection processing, a “Kernel Regularizer” that performs regularization, and a “ReLU” layer that performs ReLU processing, and the layer group Compile B1 includes a full connection layer “Linear” that performs full connection processing and an “Adagrad” layer that performs optimization processing. An input unit of the full connection layer of the layer group Compile Al corresponds to an input layer, an output unit of the layer group Compile B1 corresponds to an output layer, and each unit therebetween corresponds to an intermediate layer (hidden layer). The intermediate layer includes a Dropout layer that limits some input values to zero and prevents overfitting.
Compile A1 and A2 each include a full connection layer “Linear” that performs full connection processing, a “Kernel Regularizer” that performs regularization, and a “ReLU” layer that performs ReLU processing, and the layer group Compile B1 includes a full connection layer “Linear” that performs full connection processing and an “Adagrad” layer that performs optimization processing. An input unit of the full connection layer of the layer group Compile Al corresponds to an input layer, an output unit of the layer group Compile B1 corresponds to an output layer, and each unit therebetween corresponds to an intermediate layer (hidden layer). The intermediate layer includes a Dropout layer that limits some input values to zero and prevents overfitting.
For example, Logistic Regression provided in a Python open-source machine learning library Scikit-learn may be used in the machine learning by logistic regression. The number of dimensions may be reduced by primary component analysis as necessary. The creatinine risk obtained through a blood examination was compared with the creatinine risk estimated value obtained 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 Example 1 below.
The learning processing unit 35 stores the creatinine 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 creatinine risk estimation will be described below. However, aspects of the creatinine 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, 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, as illustrated in
In this case, data described below was selected and used as the attribute information and the non-invasive biological data. (A) the attribute information: sex, (B) the non-invasive biological data: the BMI, the blood pressure, the pulse pressure, pulse wave data, d/a, electrocardiogram data, the breathing rate, the biological impedance, 1 forehead left-side-2 left hand/delta SCR C-SCR A, 5 left hand-6 left foot/SCR C, 7 right hand-8 right foot/SCR A, 15 right hand-16 forehead left-side SCRA, ESG 2+4+15+17 (μS/m), ESG 6+8+19+21 (μS/m), ESG 9+10 (%), and R (52), where ESG 9+10 is the average of impedance values measured at the sites illustrated in
In addition, the cardiac output included in the biological impedance and the oxygen transport amount estimated from the oxygen saturation (SpO2) are included in the non-invasive biological data.
With a learning model 2, machine learning was performed by using the neural network (NN_1 or NN_2) in
In addition, the non-invasive biological data includes the singe-output amount obtained by dividing the cardiac output by the heart rate, and the oxygen transport amount estimated based on the cardiac output and the oxygen saturation (SpO2) included in the biological impedance.
In Example 1, the creatinine risk 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 creatinine obtained through a blood examination performed on the same day as the non-invasive biological information measurement for a total of 468 male subjects.
Then, an estimation result was evaluated by using an ROC_AUC curve for the estimation accuracy of the creatinine 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 1 is illustrated in
In Example 2, the creatinine 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 creatinine obtained through a blood examination performed on the same day as the non-invasive biological information measurement for a total of 244 female subjects.
Then, an estimation result was evaluated by using an ROC_AUC curve for the estimation accuracy of the creatinine risk estimation model. As a result, ROC_AUC was 0.83, which exceeds 0.8 indicating extremely favorable classification. The ROC_AUC curve of the estimation result in Example 2 is illustrated in
In the above-described embodiment, the creatinine risk is estimated by using the learning model 1 or the learning model 2, but the creatinine risk may be estimated by using a plurality of learning models.
Accordingly, the creatinine risk can be estimated at higher accuracy than the creatinine 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 creatinine 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 creatinine 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 |
|---|---|---|---|
| 2021-130216 | Aug 2021 | JP | national |
| 2022-040639 | Mar 2022 | JP | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/JP2022/015104 | 3/28/2022 | WO |
