JP2022080166A - Heart beat information acquisition device and heart beat information acquisition program - Google Patents

Abstract

To control acquisition of waveforms on the basis of an approximation degree of a plurality of heart beat waveforms corresponding to a predetermined number of heart beats in a device for acquiring blood flow information.SOLUTION: A heart beat information acquisition device includes: a waveform acquisition unit for acquiring heart beat waveforms of one or a plurality of patients; a feature amount calculation unit for calculating a feature amount of the heart beat waveforms acquired by the waveform acquisition unit; an approximation degree calculation unit for calculating an approximation degree of the feature amount of the heart beat waveforms calculated by the feature amount calculation unit; and a control unit for controlling the acquisition of the heart beat waveforms by the waveform acquisition unit. The feature amount calculation unit calculates a feature amount of one heart beat waveform and feature amounts of other heart beat waveforms in a predetermined number of continuous heart beat waveforms in one patient. The approximation degree calculation unit calculates an approximation degree of a feature amount of one heart beat waveform and feature amounts of other heart beat waveforms. The control unit controls the acquisition of the heart beat waveforms by the waveform acquisition unit on the basis of the approximation degree calculated by the approximation degree calculation unit.SELECTED DRAWING: Figure 1

Description

The present invention relates to a heart rate information acquisition device and a heart rate information acquisition program.

Patent Document 1 relates to a biological information acquisition device and a program. Patent Document 1 describes, "In addition, depending on the determination result that the number of addition averaging of the determination processing unit 90 is sufficient, the execution of the addition averaging by the signal processing unit 50 may be stopped." (Paragraph 0066).
Patent Document 2 relates to an ultrasonic diagnostic apparatus and the like. Patent Document 2 states, "For example, when the probe 100 leaves the patient, the non-contact input device 200 generates an input signal to the device body 1000 in order to freeze the currently available image." (Paragraph 0020).
[Prior Art Document]
[Patent Document]
[Patent Document 1] Japanese Patent Application Laid-Open No. 2019-76374 [Patent Document 2] Japanese Patent Application Laid-Open No. 2013-180207

In the first aspect of the present invention, a heart rate information acquisition device is provided. The heartbeat information acquisition device is calculated by a waveform acquisition unit that acquires the heartbeat waveform of one or more patients, a feature amount calculation unit that calculates the feature amount of the heartbeat waveform acquired by the waveform acquisition unit, and a feature amount calculation unit. It is provided with an approximation degree calculation unit for calculating the approximation degree of the feature amount of the heartbeat waveform, and a control unit for controlling the acquisition of the heartbeat waveform by the waveform acquisition unit. The feature amount calculation unit calculates the feature amount of one heartbeat waveform and the feature amount of another heartbeat waveform in a predetermined number of continuous heartbeat waveforms in one patient. The approximation degree calculation unit calculates the degree of approximation between the feature amount of one heartbeat waveform and the feature amount of another heartbeat waveform. The control unit controls the acquisition of the heartbeat waveform by the waveform acquisition unit based on the approximation degree calculated by the approximation degree calculation unit.

The feature amount may include the amplitude of the heartbeat waveform. The feature amount calculation unit may calculate the amplitude of one heartbeat waveform and the amplitude of another heartbeat waveform. The approximation degree calculation unit may calculate the amplitude approximation degree between the amplitude of one heartbeat waveform and the amplitude of another heartbeat waveform. When the amplitude approximation degree is equal to or higher than the predetermined amplitude approximation degree, the control unit may stop the acquisition of the heartbeat waveform by the waveform acquisition unit.

The feature amount may include the frequency of the heartbeat waveform. The feature amount calculation unit may calculate the frequency of one heartbeat waveform and the frequency of another heartbeat waveform. The approximation degree calculation unit may calculate the frequency approximation degree between the frequency of one heartbeat waveform and the frequency of another heartbeat waveform. When the frequency approximation degree is equal to or higher than the predetermined frequency approximation degree, the control unit may stop the acquisition of the heartbeat waveform by the waveform acquisition unit.

The feature amount may include the period of the heartbeat waveform. The feature amount calculation unit may calculate the cycle of one heartbeat waveform and the cycle of another heartbeat waveform. The approximation degree calculation unit may calculate the periodic approximation degree between the cycle of one heartbeat waveform and the cycle of another heartbeat waveform. When the periodic approximation degree is equal to or higher than the predetermined periodic approximation degree, the control unit may stop the acquisition of the heartbeat waveform by the waveform acquisition unit.

When the degree of approximation is less than a predetermined degree of approximation, the control unit may continue to acquire the heartbeat waveform by the waveform acquisition unit.

After continuing the acquisition of the heartbeat waveform by the waveform acquisition unit, the control unit may stop the acquisition of the heartbeat waveform by the waveform acquisition unit when the degree of approximation becomes equal to or higher than a predetermined degree of approximation.

The control unit may control the acquisition of the heartbeat waveform by the waveform acquisition unit based on another predetermined degree of approximation smaller than the predetermined degree of approximation.

The heartbeat information acquisition device may further include a storage unit that stores the heartbeat waveform acquired by the waveform acquisition unit. The feature amount calculation unit may calculate the feature amount in the heartbeat waveform stored in the storage unit. The approximation degree calculation unit may calculate the approximation degree between the feature amount of one heartbeat waveform and the feature amount of the heartbeat waveform stored in the storage unit. The control unit may control a predetermined number of continuous heartbeat waveforms based on the degree of approximation between the feature amount of one heartbeat waveform and the feature amount of the heartbeat waveform stored in the storage unit.

The feature amount calculation unit is a feature amount of the first heartbeat waveform in a predetermined number of continuous heartbeat waveforms and a feature of the second heartbeat waveform which is the next heartbeat waveform of the first heartbeat waveform in one patient. The amount and the feature amount of the third heartbeat waveform, which is the next heartbeat waveform of the second heartbeat waveform, may be calculated. The approximation degree calculation unit calculates the degree of approximation between the feature amount of the first heartbeat waveform and the feature amount of the second heartbeat waveform, and the degree of approximation between the feature amount of the second heartbeat waveform and the feature amount of the third heartbeat waveform. It's okay. In the control unit, the degree of approximation between the feature amount of the first heartbeat waveform and the feature amount of the second heartbeat waveform and the degree of approximation between the feature amount of the second heartbeat waveform and the feature amount of the third heartbeat waveform are predetermined. If the degree of approximation is equal to or higher than the above, the acquisition of the heartbeat waveform by the waveform acquisition unit may be stopped.

The waveform acquisition unit may acquire the heartbeat waveform of the first patient and the heartbeat waveform of the second patient. The feature amount calculation unit may calculate the first feature amount in the heartbeat waveform of the first patient and the second feature amount in the heartbeat waveform of the second patient. The approximation degree calculation unit may calculate the approximation degree of the first feature amount and the approximation degree of the second feature amount. When the approximation degree of the first feature amount is equal to or higher than the predetermined first approximation degree, the control unit stops the acquisition of the heartbeat waveform in the first patient by the waveform acquisition unit, and the approximation degree of the second feature amount becomes. If it is equal to or higher than the predetermined second approximation degree, the acquisition of the heartbeat waveform in the second patient by the waveform acquisition unit may be stopped. The first degree of approximation and the second degree of approximation may be different.

In the second aspect of the present invention, a heart rate information acquisition program is provided. The heart rate information acquisition program causes the computer to function as a heart rate information acquisition device.

The outline of the above invention does not list all the necessary features of the present invention. A subcombination of these feature groups can also be an invention.

It is a figure which shows an example of the block diagram of the heart rate information acquisition apparatus 100 which concerns on one Embodiment of this invention. It is a figure which shows an example of at least a part of the body of a patient 22. It is a figure which shows an example of the heartbeat waveform 12 acquired by the waveform acquisition unit 10. It is a figure which shows another example of the heartbeat waveform 12 acquired by the waveform acquisition unit 10. It is a figure which shows another example of the heartbeat waveform 12 acquired by the waveform acquisition unit 10. It is a figure which shows another example of the heartbeat waveform 12 acquired by the waveform acquisition unit 10. It is a figure which shows an example of the heartbeat waveform 126 acquired by the waveform acquisition unit 10. It is a figure which shows an example of the heart rate waveform 12-1. It is a figure which shows an example of the heart rate waveform 12-2. It is a figure which shows an example of the heart rate information acquisition method which concerns on one Embodiment of this invention. It is a figure which shows an example of the details of the stage S104 and the stage S108 in FIG. It is a figure which shows an example of the computer 2200 which the heart rate information acquisition apparatus 100 of this invention may embody wholely or partially.

Hereinafter, the present invention will be described through embodiments of the invention, but the following embodiments do not limit the invention within the scope of the claims. Also, not all combinations of features described in the embodiments are essential to the means of solving the invention.

FIG. 1 is a diagram showing an example of a block diagram of a heart rate information acquisition device 100 according to an embodiment of the present invention. The heart rate information acquisition device 100 includes a waveform acquisition unit 10, a feature amount calculation unit 20, an approximation degree calculation unit 30, and a control unit 40. The heart rate information acquisition device 100 is a computer including, for example, a CPU, a memory, an interface, and the like.

The heart rate information acquisition device 100 may include an input unit 70, an image display unit 50, and a storage unit 60. The image display unit 50 is, for example, a computer monitor, a display, or the like. The input unit 70 is, for example, a computer keyboard, a mouse, or the like. The storage unit 60 is a computer hard disk or the like. The storage unit 60 may be a hard disk or the like built in the computer, or may be a hard disk or the like external to the computer. When the heartbeat information acquisition device 100 is a computer, a heartbeat information acquisition program for making the computer function as the heartbeat information acquisition device 100 may be installed in the computer.

The heart rate information acquisition device 100 may include a blood flow sound acquisition unit 80. The blood flow sound acquisition unit 80 acquires the blood flow sound of the patient. The blood flow sound acquisition unit 80 is, for example, a stethoscope. The blood flow sound acquisition unit 80 may be an electronic stethoscope. The blood flow sound acquisition unit 80 transmits the acquired blood flow sound to the waveform acquisition unit 10.

The waveform acquisition unit 10 acquires the heartbeat waveform of one or a plurality of patients. The heartbeat waveform is a waveform of the sound of blood flow sent from the heart by the heartbeat of the patient's heart. The blood flow sound may be acquired by the blood flow sound acquisition unit 80. In this example, the waveform acquisition unit 10 acquires the waveform of the blood flow sound from the blood flow sound acquired by the blood flow sound acquisition unit 80. The heartbeat waveform acquired by the waveform acquisition unit 10 may be displayed on the image display unit 50.

The feature amount calculation unit 20 calculates the feature amount of the heartbeat waveform acquired by the waveform acquisition unit 10. As will be described later, the feature amount of the heartbeat waveform is, for example, at least one of the amplitude, frequency, and period of the heartbeat waveform. The approximation degree calculation unit 30 calculates the approximation degree of the feature amount of the heartbeat waveform calculated by the feature amount calculation unit 20. The control unit 40 controls the acquisition of the heartbeat waveform by the waveform acquisition unit 10. The control unit 40 is, for example, a CPU.

FIG. 2 is a diagram showing an example of at least a part of the body of patient 22. In this example, it is assumed that the patient 22 is receiving artificial dialysis treatment. In this example, at least a portion of the patient 22's body is the patient 22's arm. At least a portion of the patient 22's body may be the non-dominant arm of the patient 22.

In the artificial dialysis treatment, the blood of the patient 22 is drawn out of the body of the patient 22 by providing the shunt 24 on the body of the patient 22. The shunt 24 may be implanted in the body of the patient 22. The shunt 24 may be connected to the blood vessel 26 of the patient 22 within the body of the patient 22. The blood vessel 26 is at least one of the veins and arteries of patient 22. In FIG. 2, the blood vessel 26 and the shunt 24 are shown by dashed and solid lines, respectively.

If the shunt 24 is implanted in the body of the patient 22, the shunt 24 is not visible. In FIG. 2, the shunt 24 is visually shown in order to display the position where the shunt 24 is provided in the body of the patient 22.

At least one of the nurse, clinical laboratory technician, doctor and patient 22 may inspect the blood vessel 26 of the patient 22. In the present specification, at least one of a nurse, a clinical laboratory technician, a doctor and a patient 22 is referred to as a nurse or the like. The nurse or the like may inspect whether or not the blood vessel 26 of the patient 22 has a vascular stenosis.

The blood vessel 26 may be auscultated by the blood flow sound acquisition unit 80 (see FIG. 1). Blood vessel 26 may be examined by auscultation. Whether or not the blood vessel 26 has a vascular stenosis may be examined by auscultation. The blood flow sound acquisition unit 80 may acquire a shunt sound. The shunt sound is a blood flow sound of blood flowing through the shunt 24. The blood flow sound acquisition unit 80 may acquire the blood flow sound of the blood vessel 26.

The heartbeat of the patient is defined as the heartbeat Hb. Of the plurality of continuous heartbeats Hb of the patient, four continuous heartbeats Hb are designated as heartbeats Hb1 to heartbeats Hb4. The continuous heartbeats Hb1 to Hb4 means that the heartbeat Hb2 is the heartbeat next to the heartbeat Hb1, the heartbeat Hb3 is the heartbeat next to the heartbeat Hb2, and the heartbeat Hb4 is the heartbeat next to the heartbeat Hb3. Point to.

FIG. 3 is a diagram showing an example of the heartbeat waveform 12 acquired by the waveform acquisition unit 10. The heartbeat waveform 12 is a heartbeat waveform corresponding to a plurality of continuous heartbeats Hb when the patient's heartbeat Hb is measured. The heartbeat waveform 13 is a heartbeat waveform corresponding to one heartbeat Hb of the heartbeat waveforms 12. In FIG. 3, a heartbeat waveform 13 corresponding to four continuous heartbeats Hb among a plurality of continuous heartbeats Hb is shown. The heartbeat waveforms 13-1 to 13-4 correspond to heartbeats Hb1 to Hb4, respectively. The heartbeat waveforms 13-1 to 13-4 are referred to as the first heartbeat waveform 13-1 to the fourth heartbeat waveform 13-4, respectively.

The feature amount calculation unit 20 (see FIG. 1) calculates the feature amount of one heartbeat waveform 13 and the feature amount of another heartbeat waveform 13 in a predetermined number of continuous heartbeat waveforms 13 in one patient 22. calculate. In this example, the feature amount calculation unit 20 calculates the feature amount of the first heartbeat waveform 13-1, the feature amount of the second heartbeat waveform 13-2, and the feature amount of the third heartbeat waveform 13-3. The characteristic amount of the heartbeat waveform 13 is one heartbeat waveform 13 (first heartbeat waveform 13-1) corresponding to one heartbeat Hb (heartbeat Hb1) and another one corresponding to another heartbeat Hb (heartbeat Hb2). It is a feature amount that serves as a criterion for determining whether or not the heartbeat waveform 13 (second heartbeat waveform 13-2) of the above is close to each other.

One heartbeat waveform 13 may be at least one of the first heartbeat waveform 13-1 to the fourth heartbeat waveform 13-4. The other heartbeat waveform 13 may be at least one of the first heartbeat waveform 13-1 to the fourth heartbeat waveform 13-4, and may be another heartbeat waveform 13 different from the one heartbeat waveform 13. In this example, one heartbeat waveform 13 is referred to as a first heartbeat waveform 13-1, and the other heartbeat waveforms 13 are referred to as a second heartbeat waveform 13-2 and a third heartbeat waveform 13-3.

The approximation degree calculation unit 30 (see FIG. 1) calculates the degree of approximation between the feature amount of one heartbeat waveform 13 and the feature amount of another heartbeat waveform 13. In this example, the degree of approximation between the feature amount of the first heartbeat waveform 13-1 and the feature amount of the second heartbeat waveform 13-2, and the feature amount of the first heartbeat waveform 13-1 and the third heartbeat waveform 13- The degree of approximation with the feature amount of 3 is calculated. That is, in this example, the approximation degree calculation unit 30 calculates the approximation degree of two heartbeat waveforms 13 selected from three consecutive heartbeat waveforms 13 for a combination of different heartbeat waveforms 13.

The degree of approximation between the feature amount of one heartbeat waveform 13 and the feature amount of the other heartbeat waveform 13 is defined as the degree of approximation Cs. The degree of approximation between the feature amount of the first heartbeat waveform 13-1 and the feature amount of the second heartbeat waveform 13-2 is defined as the degree of approximation Cs1. The degree of approximation between the feature amount of the second heartbeat waveform 13-2 and the feature amount of the third heartbeat waveform 13-3 is defined as the degree of approximation Cs2.

The control unit 40 controls the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the approximation degree Cs of the feature amount of the heartbeat waveform 13 calculated by the approximation degree calculation unit 30. In this example, the control unit 40 controls the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the degree of approximation Cs1 and the degree of approximation Cs2. The control unit 40 may stop or continue the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the approximation degree Cs of the feature amount of the heartbeat waveform 13. The control unit 40 may stop or continue the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the degree of approximation Cs1 and the degree of approximation Cs2.

In this example, the approximation degree calculation unit 30 may calculate only the feature amount of the first heartbeat waveform 13-1 and the feature amount of the second heartbeat waveform 13-2. That is, the approximation degree calculation unit 30 may calculate only the approximation degree of two consecutive heartbeat waveforms 13 corresponding to two consecutive heartbeats Hb1 and Hb2. The control unit 40 may control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based only on the degree of approximation Cs1. However, in order for the waveform acquisition unit 10 to acquire the heartbeat waveform 12 in which the nurse or the like can inspect the state of the shunt 24 and the blood vessel 26 of the patient 22, the control unit 40 is based on the degree of approximation Cs1 and the degree of approximation Cs2. Therefore, it is preferable to control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10.

The approximation degree calculation unit 30 may further calculate the approximation degree between the feature amount of the third heartbeat waveform 13-3 and the feature amount of the first heartbeat waveform 13-1. The degree of approximation is defined as the degree of approximation Cs3. The control unit 40 may control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the degree of approximation Cs1, the degree of approximation Cs2, and the degree of approximation Cs3. When the control unit 40 controls the acquisition of the heartbeat waveform 12 based on the approximation degree Cs1, the approximation degree Cs2 and the approximation degree Cs3, it is more than the case where the control unit 40 controls the acquisition of the heartbeat waveform 12 based on the approximation degree Cs1 and the approximation degree Cs2. The control unit 40 can more precisely control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10.

In the artificial dialysis treatment, the state of the blood vessel 26 and the shunt 24 of the patient 22 is determined based on the heartbeat waveform 12. In order for a nurse or the like to determine the state of the blood vessel 26 and the shunt 24 of the patient 22, in the plurality of continuous heartbeat waveforms 13 included in the heartbeat waveform 12, the feature amount of one heartbeat waveform 13 and the other heartbeat waveforms It is preferable that the feature amount of 13 is equal to or higher than a predetermined degree of approximation. That is, in order for a nurse or the like to determine the state of the blood vessel 26 and the shunt 24 of the patient 22, the shapes of a plurality of predetermined continuous heartbeat waveforms 13 included in the heartbeat waveform 12 are close to each other. It is preferable to have.

The predetermined degree of approximation of the feature amount of the heartbeat waveform 13 is defined as the degree of approximation Cd. In the heartbeat information acquisition device 100 of this example, when the approximation degree Cs of the feature amount of the heartbeat waveform 13 is equal to or greater than the approximation degree Cd, the control unit 40 stops the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10. Therefore, the nurse or the like does not have to manually stop the acquisition of the heart rate waveform 12.

When the approximation degree Cs of the feature amount of the heartbeat waveform 13 is less than the approximation degree Cd, the control unit 40 may continue to acquire the heartbeat waveform 12 by the waveform acquisition unit 10. After continuing the acquisition of the heartbeat waveform 12, the control unit 40 may stop the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 when the approximation degree Cs of the feature amount of the heartbeat waveform 13 becomes the approximation degree Cd or more. .. In the plurality of continuous heartbeat waveforms 13 included in the heartbeat waveform 12, the control unit 40 has an approximation degree Cs of less than the approximation degree Cd between the feature amount of one heartbeat waveform 13 and the feature amount of the other heartbeat waveform 13. In this case, the acquisition of the heartbeat waveform 12 may be continued until the approximation degree Cs becomes the approximation degree Cd or more.

In the heart rate information acquisition device 100 of this example, when the approximation degree Cs of the feature amount of the heartbeat waveform 13 is less than the approximation degree Cd, the control unit 40 continues to acquire the heartbeat waveform 12 by the waveform acquisition unit 10 and the approximation degree. When Cs becomes the approximation degree Cd or more, the control unit 40 stops the acquisition of the heartbeat waveform 12. Therefore, the nurse or the like does not have to determine whether to continue or stop the acquisition of the heart rate waveform 12.

When the control unit 40 continues to acquire the heartbeat waveform 12 by the waveform acquisition unit 10, the control unit 40 uses the waveform acquisition unit 10 to obtain the heartbeat waveform based on another predetermined approximation degree smaller than the approximation degree Cd. You may control the acquisition of twelve. The other predetermined degree of approximation is defined as the degree of approximation Cd'. When the control unit 40 continues to acquire the heartbeat waveform 12 by the waveform acquisition unit 10, the control unit 40 determines the waveform acquisition unit 10 when the approximation degree Cs of the feature amount of the heartbeat waveform 13 becomes the approximation degree Cd'or higher. The acquisition of the heartbeat waveform 12 may be stopped.

The amplitude of the peak-to-peak of the heartbeat waveform 13 is defined as the amplitude Ap. The amplitude Ap may be the amplitude of the voltage [V] of the heartbeat waveform 13, or may be the amplitude of the intensity [dB] of the blood flow sound related to the heartbeat waveform 13.

The amplitudes of the peak-to-peak of the first heartbeat waveform 13-1 to the fourth heartbeat waveform 13-4 are defined as amplitude Ap1 to amplitude Ap4, respectively. The feature amount of the heartbeat waveform 13 calculated by the feature amount calculation unit 20 may include the amplitude (amplitude Ap) of the heartbeat waveform 13. The amplitude of the heart rate waveform 13 may be the amplitude of peak-to-peak of the heart rate waveform 13, or may be the amplitude of rms of the heart rate waveform 13.

The feature amount calculation unit 20 may calculate the amplitude of one heartbeat waveform 13 and the amplitude of another heartbeat waveform 13. In this example, the feature amount calculation unit 20 calculates the amplitude Ap1 of the first heartbeat waveform 13-1, and calculates the amplitude Ap2 of the second heartbeat waveform 13-2 and the amplitude Ap3 of the third heartbeat waveform 13-3. .. The approximation degree calculation unit 30 may calculate the amplitude approximation degree between the amplitude of one heartbeat waveform 13 and the amplitude of another heartbeat waveform 13. In this example, the approximation calculation unit 30 has an amplitude approximation between the amplitude Ap1 of the first heartbeat waveform 13-1 and the amplitude Ap2 of the second heartbeat waveform 13-2, and the amplitude of the first heartbeat waveform 13-1. The amplitude approximation between Ap1 and the amplitude Ap3 of the third heartbeat waveform 13-3 is calculated.

The amplitude approximation may be the ratio of the amplitude of the other heartbeat waveform 13 to the amplitude of the one heartbeat waveform 13 when the amplitude of one heartbeat waveform 13 is larger than the amplitude of the other heartbeat waveform 13. In this example, the amplitude approximations in this case are Vp2 / Vp1 and Vp3 / Vp1. The amplitude approximation may be the ratio of the amplitude of one heartbeat waveform 13 to the amplitude of the other heartbeat waveform 13 when the amplitude of one heartbeat waveform 13 is smaller than the amplitude of the other heartbeat waveform 13. In this example, the amplitude approximations in this case are Vp1 / Vp2 and Vp1 / Vp3. When the amplitude of one heartbeat waveform 13 and the amplitude of the other heartbeat waveform 13 are equal, the amplitude approximation degree is 100%.

The degree of approximation between the amplitude of one heartbeat waveform 13 and the amplitude of the other heartbeat waveform 13 is defined as the amplitude approximation degree Csa. The amplitude approximation degree between the amplitude of the first heartbeat waveform 13-1 and the amplitude of the second heartbeat waveform 13-2 is defined as the amplitude approximation degree Csa1. The amplitude approximation degree between the amplitude of the first heartbeat waveform 13-1 and the amplitude of the third heartbeat waveform 13-3 is defined as the amplitude approximation degree Csa2.

The control unit 40 may control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the amplitude approximation degree Csa1 and the amplitude approximation degree Csa2. The control unit 40 may stop or continue the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the amplitude approximation degree Csa1 and the amplitude approximation degree Csa2.

A predetermined degree of approximation of the amplitude of the heartbeat waveform 13 is defined as an amplitude approximation degree Cda. When the amplitude approximation degree Csa is equal to or higher than the amplitude approximation degree Cda, the control unit 40 may stop the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10. When the amplitude approximation degree Csa is less than the amplitude approximation degree Cda, the control unit 40 may continue to acquire the heartbeat waveform 12 by the waveform acquisition unit 10. The amplitude approximation Cda may be 80% or more and 100% or less, 90% or more and 100% or less, or 95% or more and 100% or less.

The amplitude approximation degree Cda may be stored in the storage unit 60. The amplitude approximation Cda may be updated for each examination of the condition of the shunt 24 and the blood vessel 26. The amplitude approximation Cda may be updated by a nurse or the like. When the amplitude approximation degree Csa is equal to or higher than the updated amplitude approximation degree Cda, the control unit 40 may stop the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10. The storage unit 60 may store the amplitude approximation degree Cda for each of the plurality of patients 22.

The frequency of the heartbeat waveform 13 is defined as the frequency f. The frequency f of the heartbeat waveform 13 may be a first area S1 in the power spectral density of the heartbeat waveform 13 and may be a predetermined area of the first frequency band fb1. The frequency f of the heartbeat waveform 13 may be the ratio of the first area S1 to the second area S2 in the power spectral density of the heartbeat waveform 13. The second area S2 may be a predetermined area of the second frequency band fb2. The second frequency band fb2 may include the first frequency band fb1. The frequency f of the heartbeat waveform 13 may refer to the frequency f corresponding to the largest area of the area of each frequency f in the power spectral density of the heartbeat waveform 13.

The frequency f of the first heartbeat waveform 13-1 to the fourth heartbeat waveform 13-4 is defined as a frequency f1 to a frequency f4, respectively. The feature amount of the heartbeat waveform 13 calculated by the feature amount calculation unit 20 may include the frequency f of the heartbeat waveform 13.

The feature amount calculation unit 20 may calculate the frequency f of one heartbeat waveform 13 and the frequency f of another heartbeat waveform 13. In this example, the feature amount calculation unit 20 calculates the frequency f1 of the first heartbeat waveform 13-1, and calculates the frequency f2 of the second heartbeat waveform 13-2 and the frequency f3 of the third heartbeat waveform 13-3. .. The approximation degree calculation unit 30 may calculate the frequency approximation degree between the frequency f of one heartbeat waveform 13 and the frequency f of another heartbeat waveform 13. In this example, the approximation degree calculation unit 30 has a frequency approximation degree between the frequency f1 of the first heartbeat waveform 13-1 and the frequency f2 of the second heartbeat waveform 13-2, and the frequency of the first heartbeat waveform 13-1. The frequency approximation between f1 and the frequency f3 of the third heartbeat waveform 13-3 is calculated.

The frequency approximation is the magnitude of the frequency f of the other heartbeat waveform 13 with respect to the magnitude of the frequency f of the one heartbeat waveform 13 when the frequency f of one heartbeat waveform 13 is larger than the frequency f of the other heartbeat waveform 13. It may be the ratio of the waveform. In this example, the frequency approximations in this case are f2 / f1 and f3 / f1. The frequency approximation is the magnitude of the frequency f of one heartbeat waveform 13 with respect to the magnitude of the frequency f of the other heartbeat waveform 13 when the frequency f of one heartbeat waveform 13 is smaller than the frequency f of the other heartbeat waveform 13. It may be the ratio of the waveform. In this example, the frequency approximations in this case are f1 / f2 and f1 / f3. When the frequency f of one heartbeat waveform 13 and the frequency f of the other heartbeat waveform 13 are equal, the frequency approximation degree is 100%.

The degree of approximation between the frequency of one heartbeat waveform 13 and the frequency of the other heartbeat waveform 13 is defined as the frequency approximation degree Csf. The frequency approximation degree between the frequency f1 of the first heartbeat waveform 13-1 and the frequency f2 of the second heartbeat waveform 13-2 is defined as the frequency approximation degree Csf1. The frequency approximation degree between the frequency f1 of the first heartbeat waveform 13-1 and the frequency f3 of the third heartbeat waveform 13-3 is defined as the frequency approximation degree Csf2.

The control unit 40 may control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the frequency approximation degree Csf1 and the frequency approximation degree Csf2. The control unit 40 may stop or continue the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the frequency approximation degree Csf1 and the frequency approximation degree Csf2.

A predetermined degree of approximation of the frequency of the heartbeat waveform 13 is defined as a frequency approximation degree Cdf. When the frequency approximation degree Csf is equal to or higher than the frequency approximation degree Cdf, the control unit 40 may stop the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10. When the frequency approximation degree Csf is less than the frequency approximation degree Cdf, the control unit 40 may continue to acquire the heartbeat waveform 12 by the waveform acquisition unit 10. The frequency approximation degree Cdf may be 80% or more and 100% or less, 90% or more and 100% or less, or 95% or more and 100% or less.

The frequency approximation degree Cdf may be stored in the storage unit 60. The frequency approximation Cdf may be updated for each examination of the condition of the shunt 24 and the blood vessel 26. The frequency approximation Cdf may be updated by a nurse or the like. When the frequency approximation degree Csf is equal to or higher than the updated frequency approximation degree Cdf, the control unit 40 may stop the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10. The storage unit 60 may store the frequency approximation degree Cdf for each of the plurality of patients 22.

The cycle of the heartbeat waveform 13 is defined as the cycle T. The waveform acquisition unit 10 may calculate the envelope waveform based on the time change of the blood flow sound. The waveform acquisition unit 10 may calculate the differential waveform of the envelope waveform. The waveform acquisition unit 10 may compare the amplitude of the differential waveform with the predetermined threshold value th. When the amplitude of the differential waveform is equal to or greater than a predetermined threshold value th, the control unit 40 may determine that one heartbeat Hb has been detected. The magnitude of the cycle T of the heartbeat waveform 13 is the time interval from the time when the control unit 40 determines that one heartbeat Hb is detected to the time when it is determined that the next heartbeat Hb of the one heartbeat Hb is detected. It may be there. The start of the cycle T of the heartbeat waveform 13 may be a time at which the amplitude of the heartbeat waveform 13 becomes maximum or may be a time at which the amplitude of the heartbeat waveform 13 becomes minimum.

The period T of the first heartbeat waveform 13-1 to the fourth heartbeat waveform 13-4 is defined as a frequency T1 to a frequency T4, respectively. The feature amount of the heartbeat waveform 13 calculated by the feature amount calculation unit 20 may include the period T of the heartbeat waveform 13.

The feature amount calculation unit 20 may calculate the cycle T of one heartbeat waveform 13 and the cycle T of another heartbeat waveform 13. In this example, the feature amount calculation unit 20 calculates the cycle T1 of the first heartbeat waveform 13-1, and calculates the cycle T2 of the second heartbeat waveform 13-2 and the cycle T3 of the third heartbeat waveform 13-3. .. The approximation degree calculation unit 30 may calculate the periodic approximation degree between the period T of one heartbeat waveform 13 and the period T of the other heartbeat waveform 13. In this example, the approximation degree calculation unit 30 has a periodic approximation degree between the cycle T1 of the first heartbeat waveform 13-1 and the cycle T2 of the second heartbeat waveform 13-2, and the cycle of the first heartbeat waveform 13-1. The degree of periodic approximation between T1 and the period T3 of the third heartbeat waveform 13-3 is calculated.

The cycle approximation degree is the ratio of the cycle T of the other heartbeat waveform 13 to the cycle T of the one heartbeat waveform 13 when the cycle T of one heartbeat waveform 13 is larger than the cycle T of the other heartbeat waveform 13. good. In this example, the periodic approximations in this case are T2 / T1 and T3 / T1. The cycle approximation degree is the ratio of the cycle T of one heartbeat waveform 13 to the cycle T of the other heartbeat waveform 13 when the cycle T of one heartbeat waveform 13 is smaller than the cycle T of the other heartbeat waveform 13. good. In this example, the periodic approximations in this case are T1 / T2 and T1 / T3. When the cycle T of one heartbeat waveform 13 and the cycle T of the other heartbeat waveform 13 are equal, the degree of cycle approximation is 100%.

The degree of approximation between the cycle of one heartbeat waveform 13 and the cycle of another heartbeat waveform 13 is defined as the cycle approximation degree CsT. The periodic approximation degree between the period T1 of the first heartbeat waveform 13-1 and the period T2 of the second heartbeat waveform 13-2 is defined as the periodic approximation degree CsT1. The periodic approximation degree between the period T1 of the first heartbeat waveform 13-1 and the period T3 of the third heartbeat waveform 13-3 is defined as the periodic approximation degree CsT2.

The control unit 40 may control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the periodic approximation degree CsT1 and the periodic approximation degree CsT2. The control unit 40 may stop or continue the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the periodic approximation degree CsT1 and the periodic approximation degree CsT2.

The predetermined degree of approximation of the cycle of the heartbeat waveform 13 is defined as the period approximation degree CdT. When the periodic approximation degree CsT is equal to or higher than the periodic approximation degree CdT, the control unit 40 may stop the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10. When the periodic approximation degree CsT is less than the periodic approximation degree CdT, the control unit 40 may continue to acquire the heartbeat waveform 12 by the waveform acquisition unit 10. The period approximation degree CsT may be 80% or more and 100% or less, 90% or more and 100% or less, or 95% or more and 100% or less.

The period approximation degree CdT may be stored in the storage unit 60. The periodic approximation CdT may be updated for each examination of the condition of the shunt 24 and the blood vessel 26. The period approximation CdT may be updated by a nurse or the like. When the periodic approximation degree CsT is equal to or higher than the updated periodic approximation degree CdT, the control unit 40 may stop the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10. The storage unit 60 may store the period approximation degree CdT for each of the plurality of patients 22.

FIG. 4 is a diagram showing another example of the heartbeat waveform 12 acquired by the waveform acquisition unit 10. In the heartbeat waveform 12 of this example, the amplitude of the third heartbeat waveform 13-3 is different from the amplitude of the third heartbeat waveform 13-3 shown in FIG. The peak-to-peak amplitude of the third heartbeat waveform 13-3 of this example is defined as the amplitude Ap3'. In this example, the amplitude Ap3'is larger than the amplitude Ap3.

Similar to the example of FIG. 3, one heartbeat waveform 13 is referred to as a first heartbeat waveform 13-1, and the other heartbeat waveforms 13 are referred to as a second heartbeat waveform 13-2 and a third heartbeat waveform 13-3. Similar to the example of FIG. 3, the amplitude approximation degree between the amplitude (amplitude Ap1) of the first heartbeat waveform 13-1 and the amplitude (amplitude Ap2) of the second heartbeat waveform 13-2 is defined as the amplitude approximation degree Csa1. In this example, the amplitude approximation degree between the amplitude of the first heartbeat waveform 13-1 (amplitude Ap1) and the amplitude of the third heartbeat waveform 13-3 (amplitude Ap3') is defined as the amplitude approximation degree Csa2'.

When the amplitude approximation Csa between the amplitude of one heartbeat waveform 13 and the amplitude of the other heartbeat waveform 13 is less than the amplitude approximation degree Cda, the control unit 40 continues to acquire the heartbeat waveform 12 by the waveform acquisition unit 10. It's okay. In this example, it is assumed that the amplitude approximation degree Csa1 is equal to or higher than the amplitude approximation degree Cda, but the amplitude approximation degree Csa2'is less than the amplitude approximation degree Cda. When the amplitude approximation degree Csa2'is less than the amplitude approximation degree Cda, the control unit 40 continues to acquire the heartbeat waveform 12 by the waveform acquisition unit 10. When the blood flow sound acquisition unit 80 is a stethoscope and the stethoscope deviates from a predetermined location in the body of the patient 22, the third heartbeat waveform 13-3 shown in FIG. 4 Such a heartbeat waveform 13 is easily observed.

FIG. 5 is a diagram showing another example of the heartbeat waveform 12 acquired by the waveform acquisition unit 10. In the heartbeat waveform 12 of this example, the third heartbeat waveform 13-3 is not observed. The heartbeat waveform 12 of this example is different from the third heartbeat waveform 13-3 shown in FIG. 3 in this respect. The cycle T of the second heartbeat waveform 13-2 of this example is defined as the cycle T2'. The period T2'is larger than the period T.

In this example, one heartbeat waveform 13 is referred to as the first heartbeat waveform 13-1, and the other heartbeat waveform 13 is referred to as the second heartbeat waveform 13-2. The degree of periodic approximation between the period T1 of the first heartbeat waveform 13-1 and the period T2 of the second heartbeat waveform 13-2 is defined as the degree of periodic approximation CsT1'.

When the period approximation CsT between the period T of one heartbeat waveform 13 and the period T of the other heartbeat waveform 13 is less than the period approximation degree CdT, the control unit 40 acquires the heartbeat waveform 12 by the waveform acquisition unit 10. You may continue. In this example, it is assumed that the periodic approximation CsT1'is less than the periodic approximation CdT. When the periodic approximation degree CsT1'is less than the periodic approximation degree CdT, the control unit 40 continues to acquire the heartbeat waveform 12 by the waveform acquisition unit 10. When the heartbeat Hb of the patient 22 has an arrhythmia, the heartbeat waveform 13 such as the second heartbeat waveform 13-2 shown in FIG. 5 is likely to be observed.

FIG. 6 is a diagram showing another example of the heartbeat waveform 12 acquired by the waveform acquisition unit 10. In the heartbeat waveform 12 of this example, the frequency f of the third heartbeat waveform 13-3 is different from the frequency f3 of the third heartbeat waveform 13-3 shown in FIG. The frequency f of the third heartbeat waveform 13-3 of this example is defined as the frequency f3'. The frequency f3'is smaller than the frequency f3. The frequency characteristic of the heartbeat waveform 13 when the blood vessel 26 (FIG. 2) has a vascular stenosis may be different from the frequency characteristic of the heartbeat waveform 13 before the vascular stenosis occurs. The heartbeat waveform 12 shown in FIG. 6 can be observed when a blood vessel stenosis occurs in the blood vessel 26.

Similar to the example of FIG. 3, one heartbeat waveform 13 is referred to as a first heartbeat waveform 13-1, and the other heartbeat waveforms 13 are referred to as a second heartbeat waveform 13-2 and a third heartbeat waveform 13-3. Similar to the example of FIG. 3, the frequency approximation degree between the frequency f1 of the first heartbeat waveform 13-1 and the frequency f2 of the second heartbeat waveform 13-2 is defined as the frequency approximation degree Csf1. In this example, the amplitude approximation degree between the frequency f1 of the first heartbeat waveform 13-1 and the frequency f3 of the third heartbeat waveform 13-3 is defined as the frequency approximation degree Csf2'.

When the frequency approximation Csf between the frequency f of one heartbeat waveform 13 and the frequency f of the other heartbeat waveform 13 is less than the frequency approximation degree Cdf, the control unit 40 acquires the heartbeat waveform 12 by the waveform acquisition unit 10. You may continue. In this example, it is assumed that the frequency approximation degree Csf1 is equal to or higher than the frequency approximation degree Cdf, but the frequency approximation degree Csf2'is less than the frequency approximation degree Cdf. When the frequency approximation degree Csf2'is less than the frequency approximation degree Cdf, the control unit 40 continues to acquire the heartbeat waveform 12 by the waveform acquisition unit 10. When the blood flow sound acquisition unit 80 acquires noise outside the heartbeat information acquisition device 100, it is easy to observe a heartbeat waveform 13 such as the third heartbeat waveform 13-3 shown in FIG.

The control unit 40 may control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on at least one of the amplitude approximation degree Csa, the frequency approximation degree Csf, and the periodic approximation degree CsT. The control unit 40 may control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on a plurality of approximation degrees Cs selected from the amplitude approximation degree Csa, the frequency approximation degree Csf, and the periodic approximation degree CsT. When the control unit 40 controls the waveform acquisition unit 10 based on the plurality of approximation degrees Cs, the control unit 40 acquires the heartbeat waveform 12 as compared with the case where the waveform acquisition unit 10 is controlled based on one approximation degree Cs. And continuation can be precisely controlled.

FIG. 7 is a diagram showing an example of the heartbeat waveform 126 acquired by the waveform acquisition unit 10. The heart rate information acquisition device 100 may further include a storage unit 60 (see FIG. 1) that stores the heart rate waveform 126. That is, the heartbeat waveform 126 is a heartbeat waveform stored in the storage unit 60. When the nurse or the like examines the patient 22, the heartbeat waveform 126 is a heartbeat waveform acquired at a timing different from that of the heartbeat waveform 12. The heartbeat waveform 12 (see FIGS. 3 to 6) is, for example, a heartbeat waveform acquired by the waveform acquisition unit 10 in the current examination. The heartbeat waveform 126 is, for example, a heartbeat waveform acquired by the waveform acquisition unit 10 in an inspection several days before the present.

In this example, it is assumed that the heartbeat waveform 12 shown in FIG. 3 is acquired in the current examination, and the heartbeat waveform 126 is acquired in the examination several days before the present. One heartbeat waveform in the heartbeat waveform 126 is referred to as a heartbeat waveform 136. The amplitudes of the heartbeat waveforms 136-1 to 136-4 are set to amplitude Ap1'' to amplitude Ap4'', respectively. In this example, the amplitudes (amplitude Ap1'' to amplitude Ap4'') of the heartbeat waveforms 136-1 to 136-4 are the amplitudes (amplitudes) of the first heartbeat waveforms 13-1 to the fourth heartbeat waveforms 13-4. It is smaller than Ap1 to amplitude Ap4).

The feature amount calculation unit 20 may calculate the feature amount in the heartbeat waveform 126. The feature amount calculation unit 20 may calculate the feature amount of one heartbeat waveform 136 in the heartbeat waveform 126. The approximation degree calculation unit 30 may calculate the degree of approximation between the feature amount of one heartbeat waveform 13 and the feature amount of the heartbeat waveform 136. The degree of approximation is defined as the degree of approximation Csd.

The control unit 40 may control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 based on the degree of approximation Csd. The control unit 40 may control whether or not the waveform acquisition unit 10 acquires the heartbeat waveform 12 after the heartbeat waveform 126 is acquired, based on the degree of approximation Csd. The degree of approximation Csd may be different from the degree of approximation Cs. As described above, the degree of approximation Cs is the degree of approximation of the two heartbeat waveforms 13 in one heartbeat waveform 12.

The control unit 40 may control a predetermined number in the continuous heart rate waveform 13 based on the degree of approximation Csd. The predetermined number of the heart rate waveform 136 at the time of acquiring the heart rate waveform 126 is defined as the waveform number N1. The predetermined number of the heart rate waveform 13 after the acquisition of the heart rate waveform 126 is defined as the waveform number N2. The control unit 40 may control whether the waveform number N2 is larger or smaller than the waveform number N1 based on the degree of approximation Csd, and controls whether the waveform number N2 is the same as the waveform number N1. good. The feature amount calculation unit 20 may calculate the feature amount of one heartbeat waveform 13 and the feature amount of another heartbeat waveform 13 in the continuous heartbeat waveform 13.

After the examination of the patient 22 by a nurse or the like, for example, several days later, the condition of the shunt 24 or the blood vessel 26 of the patient 22 may change due to the progress of vascular stenosis or the like. When the condition of the shunt 24 or the blood vessel 26 changes, the number of continuous heart rate waveforms 13 required for examining the condition of the shunt 24 or the blood vessel 26 may change. In the heartbeat information acquisition device 100 of this example, the control unit 40 can control the acquisition of the heartbeat waveform 12 by the waveform acquisition unit 10 even when the state of the shunt 24 or the blood vessel 26 changes.

The waveform acquisition unit 10 may acquire the heartbeat waveforms 12 of a plurality of patients 22. The first patient 22 and the second patient 22 selected from the plurality of patients 22 are referred to as patient 22-1 and patient 22-2, respectively. The heartbeat waveform 12 of patient 22-1 is referred to as a heartbeat waveform 12-1. The heartbeat waveform 12 of patient 22-2 is referred to as a heartbeat waveform 12-2.

FIG. 8 is a diagram showing an example of the heartbeat waveform 12-1. One heartbeat waveform 13 in the heartbeat waveform 12-1 is referred to as a heartbeat waveform 23. The amplitudes of the heartbeat waveforms 23-1 to 23-4 are defined as the amplitudes Ap21 to the amplitude Ap24, respectively.

FIG. 9 is a diagram showing an example of the heartbeat waveform 12-2. One heartbeat waveform 13 in the heartbeat waveform 12-2 is referred to as a heartbeat waveform 33. The amplitudes of the heartbeat waveforms 33-1 to 33-4 are defined as the amplitudes Ap31 to the amplitude Ap34, respectively. In this example, the amplitudes of the heartbeat waveforms 33-1 to 33-4 (amplitude Ap31 to amplitude Ap34) are smaller than the amplitudes of the heartbeat waveforms 23-1 to 23-4 (amplitude Ap21 to amplitude Ap24). ..

The feature amount calculation unit 20 may calculate the first feature amount in the heartbeat waveform 12-1 and the second feature amount in the heartbeat waveform 12-2. That is, the feature amount calculation unit 20 may calculate the feature amount of the heartbeat waveform 12 for each patient 22.

The approximation degree calculation unit 30 may calculate the approximation degree of the first feature amount and the approximation degree of the second feature amount. That is, the approximation degree calculation unit 30 may calculate the approximation degree of the heartbeat waveform 13 for each patient 22. The degree of approximation of the first feature amount is defined as the degree of approximation Csp1. The degree of approximation of the second feature amount is defined as the degree of approximation Csp2. The degree of approximation Csp1 is the degree of approximation between one heartbeat waveform 23 (for example, heartbeat waveform 23-1) and another heartbeat waveform 23 (for example, heartbeat waveform 23-2) in a plurality of continuous heartbeat waveforms 23. The degree of approximation Csp2 is the degree of approximation between one heartbeat waveform 33 (for example, heartbeat waveform 33-1) and another heartbeat waveform 33 (for example, heartbeat waveform 33-2) in a plurality of continuous heartbeat waveforms 33.

The control unit 40 may control the acquisition of the heartbeat waveform 12-1 by the waveform acquisition unit 10 based on the degree of approximation Csp1. The control unit 40 may control the acquisition of the heartbeat waveform 12-2 by the waveform acquisition unit 10 based on the degree of approximation Csp2.

When the degree of approximation Csp1 is equal to or higher than a predetermined first degree of approximation, the control unit 40 may stop the acquisition of the heartbeat waveform 12-1 by the waveform acquisition unit 10. The first degree of approximation is defined as the first degree of approximation C1. The first degree of approximation C1 may be a unique degree of approximation of patient 22-1. When the degree of approximation Csp2 is equal to or higher than a predetermined second degree of approximation, the control unit 40 may stop the acquisition of the heartbeat waveform 12-2 by the waveform acquisition unit 10. The second degree of approximation is defined as the second degree of approximation C2. The second degree of approximation C2 may be the unique degree of approximation of patient 22-2.

The first degree of approximation C1 and the second degree of approximation C2 may be different. The shape of the heartbeat waveform 12 is likely to vary from patient to patient 22. Therefore, the shape of the heartbeat waveform 13 that is determined to be able to inspect the state of the shunt 24 or the blood vessel 26 of the patient 22 is also likely to differ from patient to patient 22. In this example, the control unit 40 controls the acquisition of the heartbeat waveform 12-1 by the waveform acquisition unit 10 by the first approximation degree C1 peculiar to the patient 22-1, and the second approximation peculiar to the patient 22-2. The degree C2 controls the acquisition of the heartbeat waveform 12-2 by the waveform acquisition unit 10. Therefore, in the heart rate information acquisition device 100 of this example, the control unit 40 can control the stop and continuation of the acquisition of the heart rate waveform 12 for each patient 22.

FIG. 10 is a diagram showing an example of a heartbeat information acquisition method according to one embodiment of the present invention. FIG. 10 is an example of a heart rate information acquisition method when the heart rate information acquisition device 100 is used. In FIG. 10, a step executed by the user of the heart rate information acquisition device 100, a step executed by the blood flow sound acquisition unit 80, and a step executed by the heart rate information acquisition device 100 are separated by a coarse broken line. The user may be a nurse or the like.

Step S100 is a step in which the user starts recording the blood flow sound of the patient 22. The blood flow sound is the sound of blood flow sent from the heart by the heartbeat Hb of the patient 22. The stage S100 may be a stage in which the user activates (turns on) the heart rate information acquisition device 100 and the blood flow sound acquisition unit 80.

The step S102 is a step in which the blood flow sound acquisition unit 80 transmits the blood flow sound of the patient 22 to the heartbeat information acquisition device 100. The blood flow sound acquisition unit 80 may be an electronic stethoscope.

The step S104 is a step in which the waveform acquisition unit 10 acquires the heartbeat waveform 12. In step S104, the waveform acquisition unit 10 acquires the waveform of the blood flow sound from the blood flow sound acquired by the blood flow sound acquisition unit 80.

Step S106 is a step of determining whether or not one heartbeat Hb is detected from the heartbeat waveform 12. In step S106, it may be determined whether or not the control unit 40 has detected one heartbeat Hb. If it is determined in step S106 that one heartbeat Hb is not detected, the heartbeat information acquisition method of this example returns to step S102.

The step S108 is a step in which the feature amount calculation unit 20 calculates the feature amount of the heartbeat waveform 12. As described above, the feature amount may be at least one of the amplitude, frequency and period of the heart rate waveform 13. The heartbeat waveform 13 is a heartbeat waveform corresponding to one heartbeat Hb of the heartbeat waveforms 12.

The step S110 is a step of determining whether or not the feature amount calculation unit 20 has calculated n feature amounts. In step S110, it may be determined whether or not the control unit 40 has calculated n features. The feature amount calculation unit 20 calculates the feature amount of a predetermined number of continuous heartbeat waveforms 13 in the heartbeat waveform 12 of the patient 22 for each heartbeat waveform 13. The n number refers to the predetermined number. n is an integer of 2 or more. n is, for example, 3. If it is not determined in step S110 that n features have been calculated, the heart rate information acquisition method of this example returns to step S102.

Step S112 is a step in which the approximation degree calculation unit 30 calculates the approximation degree Cs of the feature amount. When n is 3, the approximation degree calculation unit 30 approximates the feature amount of the first heartbeat waveform 13-1 (see FIG. 3) and the feature amount of the second heartbeat waveform 13-2 (see FIG. 3). The degree Cs1 and the degree of approximation Cs2 between the feature amount of the second heartbeat waveform 13-2 (see FIG. 3) and the feature amount of the third heartbeat waveform 13-3 (see FIG. 3) may be calculated.

Step S114 is a step of determining whether or not the features are close to each other. In step S114, the control unit 40 may determine whether or not the features are close to each other. When n is 3, the control unit 40 is characterized by comparing the above-mentioned predetermined degree of approximation Cd with the degree of approximation Cs1 and comparing the degree of approximation Cd with the degree of approximation Cs2. It may be determined whether the quantities are close to each other. If it is not determined in step S114 that the feature amounts are close, the heart rate information acquisition method of this example returns to step S102.

The step S116 is a step of ordering the waveform acquisition unit 10 to stop the acquisition of the heartbeat waveform 12. In step S116, the control unit 40 may instruct the waveform acquisition unit 10 to stop the acquisition of the heartbeat waveform 12. In step S116, the control unit 40 may instruct the blood flow sound acquisition unit 80 to stop the transmission of the heartbeat waveform 12.

Step S117 is a step in which the blood flow sound acquisition unit 80 stops transmitting the blood flow sound to the heartbeat information acquisition device 100. The blood flow sound acquisition unit 80 may stop the transmission of the blood flow sound after receiving the command to stop the transmission of the heartbeat waveform 12 in the step S116.

Step S118 is a step in which the waveform acquisition unit 10 stops acquiring the heartbeat waveform 12. The waveform acquisition unit 10 may stop the acquisition of the heartbeat waveform 12 after receiving the command to stop the transmission of the heartbeat waveform 12 in the step S116.

Step S120 is a step of analyzing the acquired heartbeat waveform 12. In step S120, the control unit 40 may analyze the heartbeat waveform 12.

The step S122 is a step of displaying the analysis result of the heartbeat waveform 12 on the image display unit 50 (see FIG. 1). In step S122, the control unit 40 may display the result on the image display unit 50. Step S124 is a step in which the user confirms the analysis result displayed on the image display unit 50.

FIG. 11 is a diagram showing an example of the details of the stage S104 and the stage S108 in FIG. The step S104 is a step in which the waveform acquisition unit 10 acquires the heartbeat waveform 12. In this example, the stage S104 has a stage S1042, a stage S1044, a stage S1046 and a stage S1048. The step S108 is a step in which the feature amount calculation unit 20 calculates the feature amount of the heartbeat waveform 12. In this example, the stage S108 has a stage S1082, a stage S1084, a stage S1085, a stage S1086, a stage S1087 and a stage S1088.

The step S1042 is a step in which the waveform acquisition unit 10 receives the blood flow sound transmitted by the blood flow sound acquisition unit 80. Step S1044 is a step in which the waveform acquisition unit 10 calculates an envelope waveform based on the time change of the blood flow sound. The envelope waveform is referred to as an envelope waveform We.

Step S1046 is a step in which the waveform acquisition unit 10 calculates the differential waveform of the envelope waveform We. The differential waveform is referred to as a differential waveform dWe. In step S1047, the waveform acquisition unit 10 compares the predetermined threshold value th with the differential waveform dWe. The step S1047 may be a step in which the waveform acquisition unit 10 compares the threshold value th with the amplitude of the differential waveform dWe. The amplitude may be the peak-to-peak amplitude of the differential waveform dWe, or may be the rms amplitude of the differential waveform dWe. When the amplitude is the peak-to-peak amplitude of the differential waveform dWe, the amplitude may be the peak-to-peak amplitude at a predetermined time t. When the amplitude is the amplitude of rms of the differential waveform dWe, the amplitude may be the amplitude of rms between the predetermined time t and the predetermined time T.

The step S1048 is a step in which the waveform acquisition unit 10 determines whether or not the differential waveform dWe is equal to or higher than the threshold value th. If the waveform acquisition unit 10 does not determine that the differential waveform dWe is equal to or greater than the threshold value th (determined to be less than the threshold value th) in step S1048, the heartbeat information acquisition method of this example returns to step S1042.

As described above, the step S106 is a step of determining whether or not one heartbeat Hb is detected from the heartbeat waveform 12. In step S106, it may be determined whether or not the control unit 40 has detected one heartbeat Hb. In this example, when the waveform acquisition unit 10 determines in step S1048 that the differential waveform dWe is equal to or higher than the threshold value th, it is determined in step S106 that the control unit 40 has detected one heartbeat Hb.

The step S1082 is a step in which the feature amount calculation unit 20 acquires the heartbeat waveform 13. The heartbeat waveform 13 is a heartbeat waveform corresponding to one heartbeat Hb of the heartbeat waveforms 12.

Step S1084 is a step in which the feature amount calculation unit 20 calculates the amplitude of the heartbeat waveform 13. The amplitude may be the peak-to-peak amplitude of the heart rate waveform 13, or may be the rms amplitude of the heart rate waveform 13. In this example, the amplitude calculated by the feature amount calculation unit 20 is referred to as a feature amount F1.

The step S1085 is a step in which the feature amount calculation unit 20 calculates the cycle T of the heartbeat waveform 13. In this example, the period T calculated by the feature amount calculation unit 20 is referred to as the feature amount F2.

Steps S1086 to S1088 are steps in which the feature amount calculation unit 20 calculates the frequency f of the heartbeat waveform 13. Step S1086 is a step in which the feature amount calculation unit 20 applies a window function to the heartbeat waveform 13. The window function is a function that calculates an input value and calculates an output value, in which a value other than a predetermined range of the input value is zero. By calculating the input value by the window function, the value of the output value outside the predetermined range becomes zero.

In step S1087, the feature amount calculation unit 20 estimates the power spectral density of the heartbeat waveform 13 based on the calculation result by the window function. The feature amount calculation unit 20 may estimate the power spectral density of the heartbeat waveform 13 for each component of the frequency f included in the heartbeat waveform 13.

In step S1088, the feature amount calculation unit 20 calculates the area of a specific frequency f in the heartbeat waveform 13 based on the estimated power spectral density of the heartbeat waveform 13. The feature amount calculation unit 20 may calculate the area for each component of the frequency f included in the heartbeat waveform 13. The feature amount calculation unit 20 may use the first area S1 of the predetermined first frequency band fb1 among the areas of each component of the frequency f as the feature amount of the heartbeat waveform 13, and the feature amount calculation unit 20 may use the second area S2. The ratio of the first area S1 to the heartbeat waveform 13 may be used as the feature amount of the heartbeat waveform 13. The second area S2 may be a predetermined area of the second frequency band fb2. The second frequency band fb2 may include the first frequency band fb1. The feature amount calculation unit 20 may use the frequency f corresponding to the largest area among the areas of each component of the frequency f as the feature amount of the heartbeat waveform 13. The feature amount is referred to as a feature amount F3.

In step S108, one feature amount selected from the feature amount F1, the feature amount F2, and the feature amount F3 may be calculated. For example, when only the feature amount F1 is calculated in the step S108, the step S108 does not have to have the steps S1085 to S1088.

In step S108, two feature quantities selected from the feature quantity F1, the feature quantity F2, and the feature quantity F3 may be calculated. For example, when only the feature amount F1 and the feature amount F2 are calculated in the step S108, the step S108 does not have to have the steps S1086 to S1088.

Various embodiments of the present invention may be described with reference to flowcharts and block diagrams. In various embodiments of the invention, the block may represent (1) a stage of the process in which the operation is performed or (2) a section of the device responsible for performing the operation.

Certain steps may be performed by dedicated circuits, programmable circuits or processors. Specific sections may be implemented by dedicated circuits, programmable circuits or processors. The programmable circuit and the processor may be supplied with computer-readable instructions. The computer-readable instruction may be stored on a computer-readable medium.

The dedicated circuit may include at least one of a digital hardware circuit and an analog hardware circuit. The dedicated circuit may include at least one of an integrated circuit (IC) and a discrete circuit. The programmable circuit may include logic AND, logic OR, logic XOR, logic NAND, logic NOR or other logic operation hardware circuits. The programmable circuit may include reconfigurable hardware circuits including memory elements such as flip-flops, registers, field programmable gate arrays (FPGAs), programmable logic arrays (PLAs) and the like.

The computer readable medium may include any tangible device capable of storing instructions executed by the appropriate device. By including the tangible device in the computer readable medium, the computer readable medium having the instructions stored in the device can be executed to create a means for performing the operation specified in the flowchart or block diagram. Will be equipped with products, including.

The computer-readable medium may be, for example, an electronic storage medium, a magnetic storage medium, an optical storage medium, an electromagnetic storage medium, a semiconductor storage medium, or the like. More specifically, computer-readable media include, for example, floppy (registered trademark) disks, diskettes, hard disks, random access memory (RAM), read-only memory (ROM), erasable programmable read-only memory (EPROM or flash memory), and the like. Electrically erasable programmable read-only memory (EEPROM), static random access memory (SRAM), compact disk read-only memory (CD-ROM), digital versatile disk (DVD), Blu-ray (RTM) disk, memory stick, integrated It may be a circuit card or the like.

Computer-readable instructions may include any of assembler instructions, instruction set architecture (ISA) instructions, machine instructions, machine-dependent instructions, microcode, firmware instructions, state setting data, source code and object code. The source code and the object code may be written in any combination of one or more programming languages, including object-oriented programming languages and conventional procedural programming languages. The object-oriented programming language may be, for example, Smalltalk, JAVA®, C ++, or the like. The procedural programming language may be, for example, a "C" programming language.

Computer-readable instructions are used locally or on a local area network (LAN), wide area network (WAN), etc., to the processor or programmable circuit of a general purpose computer, special purpose computer, or other programmable data processing device. ) May be provided. The processor or programmable circuit of a general purpose computer, special purpose computer, or other programmable data processing device performs the operation specified in the flowchart shown in FIGS. 10 and 11 or the block diagram shown in FIG. Computer-readable instructions may be executed to create a means of doing so. The processor may be, for example, a computer processor, a processing unit, a microprocessor, a digital signal processor, a controller, a microcontroller, or the like.

FIG. 12 is a diagram showing an example of a computer 2200 in which the heart rate information acquisition device 100 of the present invention may be embodied in whole or in part. The program installed on the computer 2200 can cause the computer 2200 to function as one or more sections of the operation or heart rate information acquisition device 100 associated with the heart rate information acquisition device 100 according to the embodiment of the present invention. The operation or the one or more sections can be performed, or the computer 2200 can be made to perform each step (see FIGS. 10 and 11) according to the heartbeat information acquisition method of the present invention. The program causes the computer 2200 to perform certain operations associated with some or all of the blocks in the flowcharts (FIGS. 10 and 11) and block diagrams (FIG. 1) described herein. , May be executed by CPU 2212.

The computer 2200 according to this embodiment includes a CPU 2212, a RAM 2214, a graphic controller 2216, and a display device 2218. The CPU 2212, RAM 2214, graphic controller 2216 and display device 2218 are interconnected by a host controller 2210. The computer 2200 further includes an input / output unit such as a communication interface 2222, a hard disk drive 2224, a DVD-ROM drive 2226, and an IC card drive. The communication interface 2222, the hard disk drive 2224, the DVD-ROM drive 2226, the IC card drive, and the like are connected to the host controller 2210 via the input / output controller 2220. The computer further includes a legacy input / output unit such as a ROM 2230 and a keyboard 2242. The ROM 2230, the keyboard 2242, and the like are connected to the input / output controller 2220 via the input / output chip 2240.

The CPU 2212 controls each unit by operating according to the programs stored in the ROM 2230 and the RAM 2214. The graphic controller 2216 acquires the image data generated by the CPU 2212 in a frame buffer or the like provided in the RAM 2214 or the RAM 2214 so that the image data is displayed on the display device 2218.

The communication interface 2222 communicates with other electronic devices via the network. The hard disk drive 2224 stores programs and data used by the CPU 2212 in the computer 2200. The DVD-ROM drive 2226 reads the program or data from the DVD-ROM 2201 and provides the read program or data to the hard disk drive 2224 via the RAM 2214. The IC card drive reads the program and data from the IC card or writes the program and data to the IC card.

The ROM 2230 stores a boot program or the like executed by the computer 2200 at the time of activation, or a program depending on the hardware of the computer 2200. The input / output chip 2240 may connect various input / output units to the input / output controller 2220 via a parallel port, a serial port, a keyboard port, a mouse port, and the like.

The program is provided by a computer-readable medium such as a DVD-ROM 2201 or an IC card. The program is read from a computer-readable medium, installed on a hard disk drive 2224, RAM2214, or ROM2230, which is also an example of a computer-readable medium, and executed by the CPU 2212. The information processing described in these programs is read by the computer 2200 and provides a link between the program and the various types of hardware resources described above. The device or method may be configured to implement the manipulation or processing of information in accordance with the use of computer 2200.

For example, when communication is executed between the computer 2200 and an external device, the CPU 2212 executes a communication program loaded in the RAM 2214, and performs communication processing on the communication interface 2222 based on the processing described in the communication program. You may order. The communication interface 2222 reads and reads the transmission data stored in the transmission buffer processing area provided in the recording medium such as the RAM 2214, the hard disk drive 2224, the DVD-ROM 2201 or the IC card under the control of the CPU 2212. To the network, or write the received data received from the network to the receive buffer processing area provided on the recording medium.

The CPU 2212 may allow the RAM 2214 to read all or necessary parts of a file or database stored in an external recording medium such as a hard disk drive 2224, a DVD-ROM drive 2226 (DVD-ROM2201), an IC card, or the like. The CPU 2212 may perform various types of processing on the data on the RAM 2214. The CPU 2212 may then write back the processed data to an external recording medium.

Various types of information such as various types of programs, data, tables, and databases may be stored and processed in recording media. The CPU 2212 refers to the data read from the RAM 2214 with various types of operations, information processing, conditional determination, conditional branching, unconditional branching, information retrieval or information retrieval specified by the instruction sequence of the program described in the present disclosure. Various types of processing may be performed, including substitutions and the like. The CPU 2212 may write back the result to the RAM 2214.

The CPU 2212 may search for information in a file, database, or the like in the recording medium. For example, when a plurality of entries each having an attribute value of the first attribute associated with the attribute value of the second attribute are stored in the recording medium, the CPU 2212 specifies the attribute value of the first attribute. A predetermined condition is obtained by searching for an entry that matches the condition from the plurality of entries, reading the attribute value of the second attribute stored in the entry, and reading the second attribute value. The attribute value of the second attribute associated with the first attribute that satisfies the condition may be acquired.

The program or software module described above may be stored on the computer 2200 or on a computer-readable medium of the computer 2200. A recording medium such as a hard disk or RAM provided in a dedicated communication network or a server system connected to the Internet can be used as a computer readable medium. The program may be provided to the computer 2200 by the recording medium.

Although the present invention has been described above using the embodiments, the technical scope of the present invention is not limited to the scope described in the above embodiments. It will be apparent to those skilled in the art that various changes or improvements can be made to the above embodiments. It is clear from the description of the claims that the form with such changes or improvements may be included in the technical scope of the present invention.

The order of execution of each process such as operation, procedure, step, and step in the apparatus, system, program, and method shown in the claims, specification, and drawings is particularly "before" and "prior to". It should be noted that it can be realized in any order unless the output of the previous process is used in the subsequent process. Even if the scope of claims, the specification, and the operation flow in the drawings are explained using "first", "next", etc. for convenience, it means that it is essential to carry out in this order. It's not a thing.

10 ... waveform acquisition unit, 12 ... heartbeat waveform, 13 ... heartbeat waveform, 20 ... feature amount calculation unit, 22 ... patient, 23 ... heartbeat waveform, 24 ... shunt, 26 ... blood vessel, 30 ... approximation calculation unit, 33 ... heart rate waveform, 40 ... control unit, 50 ... image display unit, 60 ... storage unit, 70 ... input unit , 80 ... Blood flow sound acquisition unit, 100 ... Heart rate information acquisition device, 126 ... Heart rate waveform, 136 ... Heart rate waveform, 2200 ... Computer, 2201 ... DVD-ROM, 2210 ... Host controller, 2212 ... CPU, 2214 ... RAM, 2216 ... Graphic controller, 2218 ... Display device, 2220 ... Input / output controller, 2222 ... Communication interface, 2224 ... Hard disk drive, 2226 ... DVD-ROM drive, 2230 ... ROM, 2240 ... I / O chip, 2242 ... keyboard

Claims (11)

A waveform acquisition unit that acquires the heartbeat waveforms of one or more patients,
A feature amount calculation unit for calculating the feature amount of the heartbeat waveform acquired by the waveform acquisition unit, and a feature amount calculation unit.
An approximation degree calculation unit that calculates the degree of approximation of the feature amount of the heartbeat waveform calculated by the feature amount calculation unit, and
A control unit that controls the acquisition of the heartbeat waveform by the waveform acquisition unit,
Equipped with
The feature amount calculation unit calculates the feature amount of one heartbeat waveform and the feature amount of another heartbeat waveform in a predetermined number of continuous heartbeat waveforms in one patient.
The approximation degree calculation unit calculates the degree of approximation between the feature amount of the one heartbeat waveform and the feature amount of the other heartbeat waveforms.
The control unit controls the acquisition of the heartbeat waveform by the waveform acquisition unit based on the approximation degree calculated by the approximation degree calculation unit.
Heart rate information acquisition device. The feature amount includes the amplitude of the heartbeat waveform.
The feature amount calculation unit calculates the amplitude of the one heartbeat waveform and the amplitude of the other heartbeat waveform.
The approximation degree calculation unit calculates the amplitude approximation degree between the amplitude of the one heartbeat waveform and the amplitude of the other heartbeat waveforms.
When the amplitude approximation degree is equal to or higher than a predetermined amplitude approximation degree, the control unit stops the acquisition of the heartbeat waveform by the waveform acquisition unit.
The heart rate information acquisition device according to claim 1. The feature amount includes the frequency of the heartbeat waveform.
The feature amount calculation unit calculates the frequency of the one heartbeat waveform and the frequency of the other heartbeat waveform.
The approximation degree calculation unit calculates the frequency approximation degree between the frequency of the one heartbeat waveform and the frequency of the other heartbeat waveforms.
When the frequency approximation degree is equal to or higher than a predetermined frequency approximation degree, the control unit stops the acquisition of the heartbeat waveform by the waveform acquisition unit.
The heart rate information acquisition device according to claim 1 or 2. The feature amount includes the cycle of the heartbeat waveform.
The feature amount calculation unit calculates the cycle of the one heartbeat waveform and the cycle of the other heartbeat waveforms.
The approximation degree calculation unit calculates the periodic approximation degree between the cycle of the one heartbeat waveform and the cycle of the other heartbeat waveforms.
When the periodic approximation degree is equal to or higher than a predetermined periodic approximation degree, the control unit stops the acquisition of the heartbeat waveform by the waveform acquisition unit.
The heart rate information acquisition device according to any one of claims 1 to 3. The heartbeat information acquisition according to any one of claims 1 to 4, wherein the control unit continues to acquire the heartbeat waveform by the waveform acquisition unit when the approximation degree is less than a predetermined approximation degree. Device. After continuing the acquisition of the heartbeat waveform by the waveform acquisition unit, the control unit stops the acquisition of the heartbeat waveform by the waveform acquisition unit when the approximation degree becomes equal to or higher than a predetermined approximation degree. The heart rate information acquisition device according to claim 5. The heartbeat information acquisition according to claim 5, wherein the control unit controls the acquisition of the heartbeat waveform by the waveform acquisition unit based on another predetermined approximation degree smaller than the predetermined approximation degree. Device. Further, a storage unit for storing the heartbeat waveform acquired by the waveform acquisition unit is provided.
The feature amount calculation unit calculates the feature amount in the heartbeat waveform stored in the storage unit, and calculates the feature amount.
The approximation degree calculation unit calculates an approximation degree between the feature amount of the one heartbeat waveform and the feature amount of the heartbeat waveform stored in the storage unit.
The control unit determines a predetermined number in the continuous heartbeat waveform based on the degree of approximation between the feature amount of the one heartbeat waveform and the feature amount of the heartbeat waveform stored in the storage unit. Control,
The heart rate information acquisition device according to any one of claims 1 to 7. The feature amount calculation unit is a feature amount of the first heartbeat waveform in the predetermined number of continuous heartbeat waveforms in one patient, and a second heartbeat waveform next to the first heartbeat waveform. The feature amount of the heartbeat waveform and the feature amount of the third heartbeat waveform, which is the next heartbeat waveform after the second heartbeat waveform, are calculated.
The approximation degree calculation unit approximates the degree of approximation between the feature amount of the first heartbeat waveform and the feature amount of the second heartbeat waveform, and the feature amount of the second heartbeat waveform and the feature amount of the third heartbeat waveform. Calculate the degree and
The control unit has the approximation of the approximation between the feature amount of the first heartbeat waveform and the feature amount of the second heartbeat waveform, and the approximation of the feature amount of the second heartbeat waveform and the feature amount of the third heartbeat waveform. When the degree is equal to or higher than a predetermined degree of approximation, the acquisition of the heartbeat waveform by the waveform acquisition unit is stopped.
The heart rate information acquisition device according to any one of claims 1 to 8. The waveform acquisition unit acquires the heartbeat waveform of the first patient and the heartbeat waveform of the second patient.
The feature amount calculation unit calculates the first feature amount in the heartbeat waveform of the first patient and the second feature amount in the heartbeat waveform of the second patient.
The approximation degree calculation unit calculates the approximation degree of the first feature amount and the approximation degree of the second feature amount.
When the degree of approximation of the first feature amount is equal to or higher than a predetermined degree of approximation, the control unit stops the acquisition of the heartbeat waveform in the first patient by the waveform acquisition unit, and the second feature. When the degree of approximation of the quantity is equal to or higher than the predetermined second degree of approximation, the waveform acquisition unit stops the acquisition of the heartbeat waveform in the second patient.
The first degree of approximation and the second degree of approximation are different.
The heart rate information acquisition device according to any one of claims 1 to 9. A heartbeat information acquisition program for operating a computer as the heartbeat information acquisition device according to any one of claims 1 to 10.

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