JP6238278B2 - Pulsation measurement device, pulsation measurement method, and program - Google Patents

Description

  The present invention relates to a pulsation measuring apparatus, a pulsation measuring method, and a program capable of measuring the pulsation of a living body during exercise, in particular, the pulsation of a small experimental animal such as a guinea pig during exercise.

Conventionally, behavioral experiments represented by drinking water experiments have been generally adopted as methods for investigating conditioned learning of animals. However, a drinking experiment requires a minimum of one week including preparation. For this reason, another method for investigating conditioned learning of animals is required.
For example, as another method for investigating conditioned learning of animals, there is a method using an electrocardiogram, which is one of the methods for monitoring the psychological state of animals. However, in this method, since noise is mixed when the animal moves, it is necessary to measure the animal under restraint or under anesthesia, and it is inappropriate to apply it to the pulse measurement of the animal under free action.
Therefore, the present inventor paid attention to a method using measurement of pulsation by an ear sensor (see, for example, Patent Document 1), which is another method for monitoring the psychological state of an animal.

JP 2012-152493 A

  However, since the conventional ear sensor including Patent Document 1 is assumed to be mounted on a human earlobe during exercise or the like to measure the pulsation of the human, even if it is mounted on the ear of a guinea pig during exercise, the guinea pig It is very difficult to measure the pulsation.

  The present invention has been made in view of such a situation, and an object thereof is to make it possible to accurately measure the pulsation of a living body during exercise.

In order to achieve the above object, a pulsation measuring device according to one aspect of the present invention includes:
A light emitting unit that emits light of a predetermined wavelength;
An output unit configured to receive light emitted from the light emitting unit and transmitted through a measurement target site of a living body, and to output an electrical signal corresponding to the intensity of the light;
Based on the time transition of the electrical signal output from the output unit, an acquisition unit that acquires pulsation data in the measurement target site;
With
The wavelength of the light emitting unit is set based on a thickness and an absorption coefficient of the measurement target part.
Thus, the wavelength of the light emitting unit, which has not been considered in the past, is set based on the thickness of the measurement target region and the absorption coefficient. As a result, it is possible to measure the pulsation of a living body during exercise, particularly the pulsation of a small experimental animal such as a guinea pig during exercise.

Moreover, in the pulsation measuring device of one aspect of the present invention,
The measurement target site is an ear of a small experimental animal,
The wavelength of the light emitting unit is set in a yellow light band,
Can be.
This makes it possible to accurately and appropriately measure the pulsation of a small experimental animal such as a guinea pig during exercise.

Further, the pulsation measuring device according to one aspect of the present invention includes:
A wavelength setting unit that variably sets the wavelength of the light emitting unit based on the thickness and absorption coefficient of the measurement target part,
Can further be provided.
Thereby, it becomes possible to measure pulsation accurately and appropriately regardless of the difference in the measurement target region. Here, the difference in the measurement target part is not only the difference in the type of living body such as a human or a small experimental animal (difference in ear thickness or blood flow) but also the difference in part in the same living body (ear and it). Other parts, such as a difference from a finger or the like).

  Moreover, in order to achieve the said objective, each of the pulsation measuring method and program of 1 aspect of this invention is each of the method and program corresponding to the above-mentioned pulsation measuring apparatus of 1 aspect of this invention.

  According to the present invention, it is possible to accurately measure the pulsation of a living body during exercise.

It is a block diagram which shows the functional structure of the pulsation apparatus which concerns on one Embodiment of this invention. It is a schematic diagram which shows the external appearance structure of an LED light emission part and a light-receiving part among the pulsation measuring apparatuses of FIG. It is a schematic diagram which shows a mode that the ear sensor which consists of an LED light emission part and a light-receiving part among the pulsation measuring apparatuses of FIG. 1 was mounted | worn with the ear | edge of the guinea pig as an example of a biological body. It is a figure which shows the measurement result of the pulsation of the guinea pig of FIG. 3 by the pulsation measuring apparatus of FIG. It is a schematic diagram explaining the outline | summary of the principle of the measurement of the pulsation of a biological body by the pulsation measuring apparatus of FIG. 1 containing the ear sensor which consists of LED light emission part and a light-receiving part. It is a figure which shows the absorption spectrum of the hemoglobin about the wavelength of light. It is a schematic diagram for demonstrating the relationship between the absorption coefficient and transmittance | permeability of an object. It is a schematic diagram for demonstrating the relationship between the absorption coefficient and transmittance | permeability of an object in the case of considering scattering.

  Hereinafter, embodiments of the present invention will be described with reference to the drawings.

  FIG. 1 is a block diagram showing a functional configuration of a pulsation measuring apparatus according to an embodiment of the present invention.

  As shown in FIG. 1, the pulsation measuring device includes an LED (Light Emitting Diode) drive power supply 11, a switching unit 12, and N types of LED light emitting units 13 having different wavelengths (N is an arbitrary integer value of 1 or more). -1 to 13-N, a light receiving unit 14, an amplifier 15, a data acquisition unit 16, a data display unit 17, a thickness acquisition unit 18, and a wavelength setting unit 19.

  Here, in this embodiment, the data display unit 17 is configured as a display built in the computer 31, and the data acquisition unit 16, the thickness acquisition unit 18, and the wavelength setting unit 19 include the computer 31 (hardware) and the computer 31 (hardware). Is configured in cooperation with software executed by However, the configuration of the data acquisition unit 16 to the wavelength setting unit 19 is not particularly limited to the present embodiment, and any configuration having each function described later is sufficient. That is, for example, the data display unit 17 may be configured as an external monitor different from the computer 31, and at least some of the functions of the data acquisition unit 16, the thickness acquisition unit 18, and the wavelength setting unit 19 are dedicated. It may be configured by a circuit (hardware).

The LED drive power supply 11 is a stabilized power supply for causing the LED light emitting units 13-1 to 13-N to emit light.
The switching unit 12 switches the output destination based on the control of the LED selection unit 20. Specifically, in the switching unit 12, the LED drive power supply 11 is connected to the input end, and each of the LED light emitting units 13-1 to 13-N is connected to each of the N output ends. When the LED light emitting unit 13-K (K is an arbitrary integer value from 1 to N) is selected by the LED selection unit 20 described later, the output destination of the switching unit 12 is switched to the LED light emitting unit 13-K. It is done.
In this case, the electric power generated from the LED drive power supply 11 is supplied to the LED light emitting unit 13 -K via the switching unit 12.
LED light emission unit 13-K, the other has a LED of different wavelengths, the power that is occurs from the LED driving power supply 11 as a driving source, to emit light.
In addition, when it is not necessary to distinguish each of the LED light emission parts 13-1 thru | or 13-N in particular, these are collectively called the "LED light emission part 13" hereafter.
The light receiving unit 14 includes a photodiode, receives light from the LED light emitting unit 13, converts it into an electric signal having a level corresponding to the intensity of the received light, and outputs it.
The amplifier 15 amplifies the level of the electrical signal output from the light receiving unit 14 and outputs the amplified signal to the data acquisition unit 16 as an output signal having a predetermined current value (for example, a current value within a range of 4 to 20 mA), for example.

FIG. 2 is a schematic diagram showing the external configuration of the LED light emitting unit 13 and the light receiving unit 14.
As shown in FIG. 2, the LED light emitting unit 13 and the light receiving unit 14 constitute a so-called ear sensor that is worn on the ears of living bodies including humans.
When measuring the pulsation of the living body, the surface of the LED light emitting unit 13 on which the LED 41 is disposed (the surface shown in FIG. 2A, hereinafter referred to as “surface”) and the photodiode of the light receiving unit 14 It arrange | positions so that the surface (it is a surface shown to FIG. 2 (A), and is hereafter called "surface") may be opposed, and the ear | edge of a biological body may be pinched | interposed. In this case, as shown in FIG. 2B, the ear sensor is fixed to the ear of the living body by the magnetic force of the magnet 42 arranged on the back surface of the LED light emitting unit 13 and the magnet 43 arranged on the back surface of the light receiving unit 14. Is done.

  FIG. 3 is a schematic diagram showing a state where an ear sensor composed of the LED light emitting unit 13 and the light receiving unit 14 is attached (fixed) to an ear of a guinea pig 51 as an example of a living body.

Returning to FIG. 1, the data acquisition unit 16 acquires waveform data continuously output as an output signal from the light receiving unit 14 via the amplifier 15, and measures the pulsation of the living body based on the waveform data.
Hereinafter, the electric signal output from the light receiving unit 14 via the amplifier 15 is simply referred to as “output signal of the light receiving unit 14”. In other words, the point through the amplifier 15 will be omitted below.
The data display unit 17 displays the waveform data supplied from the light receiving unit 14 and the measurement result of the pulsation of the living body as images.

FIG. 4 is a diagram showing a measurement result of pulsation of the guinea pig 51 of FIG. 3 by the pulsation measuring device of FIG.
The vertical axis indicates the level of the output signal of the light receiving unit 14, and the horizontal axis indicates the time axis.
The data acquisition unit 16 measures the pulse of the guinea pig 51 to which the ear sensor is attached based on the period of the output signal of the light receiving unit 14 (time interval from the peak to the peak of the waveform in the figure). The data acquisition unit 16 measures the blood flow volume in the ear of the guinea pig 51 based on the amplitude H of the output signal of the light receiving unit 14.

FIG. 5 is a schematic diagram for explaining the outline of the measurement principle of the pulsation of the living body by the pulsation measuring device of FIG. 1 including the ear sensor composed of the LED light emitting unit 13 and the light receiving unit 14.
FIG. 5A shows a living tissue in a living body portion to which the ear sensor is attached (for example, the ear of the guinea pig 51 in the example of FIG. 3).
As shown in FIG. 5A, the part of the living body to which the ear sensor is attached (for example, the ear of the guinea pig 51 in the example of FIG. 3) is viewed from the side where the light receiving unit 14 comes into contact (the lower side in the figure). , tissues other than the blood vessel, vein plexus of blood vessels, and arteries layer of blood vessels, is formed by a product layer.
Therefore, the light emitted from the LED light emitting unit 13 enters the arterial layer as incident light, passes through tissues other than the venous layer and blood vessels, and is output to the outside of the living body as transmitted light, and is received by the light receiving unit 14. Is done. The light receiving unit 14 converts the electrical signal into an electrical signal of a level corresponding to the intensity of the transmitted light (in this embodiment, a current value within a range of 4 to 20 mA through the amplifier 15), and uses the electrical signal as an output signal. The data is output to the data acquisition unit 16. That is, the level of the output signal of the light receiving unit 14 (vertical axis in FIG. 4) directly indicates the intensity of transmitted light.
FIG. 5B shows the relationship between the temporal change in the thickness of the arterial layer and the temporal change in the intensity of transmitted light.
As shown in FIG. 5B, the blood flow per unit time changes with the pulsation of the heart, and blood flows while the arterial layer of the blood vessels swells or shrinks. In other words, the thickness of the arterial layer changes according to the heartbeat. As a result, the intensity of transmitted light from the living body changes according to the change in the thickness of the arterial layer.
Therefore, the pulse can be measured based on the period of the waveform of the output signal of the light receiving unit 14 (waveform indicating the temporal transition of the intensity of transmitted light). Further, based on the amplitude H of the output signal of the light receiving unit 14, the blood flow rate of the living body can be measured.

Here, the inventor adopted a conventional ear sensor disclosed in Patent Document 1 or the like as an ear sensor including the LED light emitting unit 13 and the light receiving unit 14.
However, as described above in the section of [Problems to be Solved by the Invention], the conventional ear sensor can be mounted on the earlobe of a person in motion and measure the pulsation of the person. It is practically impossible to measure the pulsation of the experimental small animal by wearing it on the ear of a small experimental animal such as the guinea pig 51.
Therefore, as a result of examining the cause in detail, the present inventor has found that the ears of small experimental animals such as guinea pigs are too thin compared to human ear lobes, resulting in insufficient blood flow necessary for measurement and optical detection. I came to the conclusion that it might be. Therefore, the present inventors have invented a unique ear sensor suitable for use in small experimental animals.
That is, in the present embodiment, as the ear sensor composed of the LED light emitting unit 13 and the light receiving unit 14, a unique ear sensor invented by the present inventor is employed. Hereinafter, the unique ear sensor will be described in detail.

  First, the inventor thinks that if the ear of the guinea pig 51 is too thin to detect because the blood flow is insufficient, the detection power may be increased, and the amplification factor of the amplifier 15 is maintained while applying the conventional ear sensor. I tried various methods such as raising However, no attempt was made to measure the pulse of small experimental animals such as the guinea pig 51 during exercise.

Therefore, the present inventor has focused on the absorption spectrum of hemoglobin.
FIG. 6 is a diagram showing an absorption spectrum of hemoglobin (Hb or HbO ₂ ) with respect to the wavelength of light.
That is, in FIG. 6, the vertical axis indicates the absorption coefficient (arbitrary unit) of hemoglobin (Hb or HbO ₂ ), and the horizontal axis indicates the wavelength (nm) of light.
In the conventional human ear sensor, near infrared light in the vicinity of 900 [nm] is generally employed. The reason for this adoption is to increase the light transmission power because the tissue of the human earlobe is thick. However, as shown in FIG. 6, the absorption coefficient of near-infrared light is low, that is, the amount of absorption by hemoglobin is low, so the amplitude H of the output signal of the light receiving unit 14 is also low enough to be buried in noise. As a result, it becomes virtually impossible to measure the pulse of a small experimental animal such as the guinea pig 51 during exercise.
Therefore, the present inventor has focused on visible light (yellow light) in the vicinity of 550 to 600 [nm]. That is, the present inventor has noted that the absorption coefficient for yellow light is nearly two digits higher than that of near infrared light. In other words, the present inventor speculated that by applying the LED light emitting unit 13 that emits the yellow light, the lack of blood flow of the guinea pig 51 is covered, and the pulsation of the guinea pig 51 can be measured. And this inventor produced the original ear sensor which consists of the LED light emission part 13 and the light-receiving part 14 which used yellow LED, this was mounted in the pulsation measuring apparatus of FIG. As a result, pulsation was successfully measured. This measurement result is shown in FIG. 4 described above.

式（１）及び式（２）において、Ｃは、モル濃度を示し、ε（λ）は、波長λの光についてのモル吸光係数（１モルあたりの吸収係数）を示している。
上述した図６に示す波長λと吸収係数α（λ）の関係（グラフ）から、とある波長λに対する吸収係数α（λ）の値がわかるので、生体の測定対象部位（ここでは耳）の厚さｄがわかれば、透過率Ｔ（λ）が求まることになる。
換言すると、脈動を測定するためには、受光部１４の出力信号の振幅Ｔが、ノイズに埋もれない程度の大きさとなっていることが必要であり、このためには、透過率Ｔ（λ）が所定の閾値以上の大きさになることが必要である。
そこで、本発明人は、生体の測定対象部位（ここでは耳）の厚さｄを入力パラメータとして、波長λの候補を変化させながら透過率Ｔ（λ）を順次求め、透過率Ｔ（λ）が閾値を超えた波長λの候補の中から、ＬＥＤ発光部１３の光の波長λを設定する、という手法を発明した。
これにより、測定対象部位の違いによらず、生体の脈動を精度よく適切に測定することが可能になる。ここで、測定対象部位の違いとは、人間や実験用小動物等の生体の種類の違い（耳の厚さｄや血流量の違い）のみならず、同一生体の中での部位の違い（耳と、それ以外の部位、例えば指等との違い）も含まれる。 The present inventor further invented the following technique and applied the technique to the pulsation measuring apparatus of FIG.
First, the relationship between the absorption coefficient and transmittance of an object will be described with reference to FIG.
FIG. 7 is a schematic diagram for explaining the relationship between the absorption coefficient and transmittance of an object.
As shown in FIG. 7, it is assumed that incident light having an intensity I 0 (λ) is transmitted through an object having a thickness d and output as transmitted light having an intensity I (λ).
In this case, the Lambert-Beer law as shown in Equation (1) or Equation (2) is known as the relationship between the absorption coefficient α (λ) of the object and the transmittance T (λ) for light of wavelength λ. It has been.

In the formulas (1) and (2), C represents the molar concentration, and ε (λ) represents the molar extinction coefficient (absorption coefficient per mole) for light having the wavelength λ.
From the relationship (graph) between the wavelength λ and the absorption coefficient α (λ) shown in FIG. 6 described above, the value of the absorption coefficient α (λ) with respect to a certain wavelength λ can be found. If the thickness d is known, the transmittance T (λ) can be obtained.
In other words, in order to measure the pulsation, it is necessary that the amplitude T of the output signal of the light receiving unit 14 be large enough not to be buried in noise. For this purpose, the transmittance T (λ) Needs to be larger than a predetermined threshold.
Therefore, the present inventor sequentially obtains the transmittance T (λ) while changing the candidate of the wavelength λ using the thickness d of the measurement target part (here, the ear) of the living body as an input parameter, and the transmittance T (λ) Has invented a method of setting the wavelength λ of the light emitted from the LED light emitting unit 13 among the candidates of the wavelength λ exceeding the threshold.
Thereby, it becomes possible to measure the pulsation of the living body accurately and appropriately regardless of the difference in the measurement target region. Here, the difference in the region to be measured is not only the difference in the type of living body such as a human being or a small experimental animal (the difference in ear thickness d or blood flow), but also the difference in the portion in the same living body (ear). And other parts such as a finger).

  Such a technique invented by the present inventor is applied to the pulsation measuring apparatus of FIG. 1, and as a result, as shown in FIG. 1, the computer 31 includes a thickness acquisition unit 18 and a wavelength setting unit 19. And are provided. Moreover, the LED selection part 20 for controlling switching of the switch part 12 is provided.

  The thickness acquisition unit 18 acquires the thickness d of the measurement target region (ear in this case) of the living body input by a user who operates a keyboard or mouse (not shown in FIG. 1) and supplies the thickness d to the wavelength setting unit 19. To do.

The wavelength setting unit 19 sets the wavelength λ of the light emitted from the LED light emitting unit 13 according to the method invented by the inventors.
That is, data that can specify the relationship (graph) between the wavelength λ and the absorption coefficient α (λ) shown in FIG. 6 is stored in a memory (not shown) of the computer 31.
Therefore, the wavelength setting unit 19 sequentially obtains the absorption coefficient α (λ) while changing the wavelength λ candidates based on the data. Then, the wavelength setting unit 19 substitutes the input thickness d and the sequentially obtained absorption coefficients α (λ) into the formula (1) or the formula (2) and sequentially calculates the transmittance. T (λ) is obtained sequentially. Of the plurality of transmittances T (λ) sequentially obtained in this way, the wavelength setting unit 19 selects the wavelength λ from the candidates for the wavelength λ when the transmittance T (λ) exceeds the threshold. Sets the wavelength λ of light.

  The LED selection unit 20 selects, as an output destination, the LED light emission unit 13-K having the wavelength set by the wavelength setting unit 19 among the LED light emission units 13-1 to 13-N as a band.

式（３）において、Ｇ（λ）は、散乱による減衰を示しており、ｌ（λ）は、散乱の場合の物体内での光路長を示しており、ｎは、散乱による光路の総数を示している。
式（３）から明らかなように、散乱がある場合には、厚さｄは用いられず、平均の光路長ｌ（λ）が用いられる。
しかしながら、平均の光路長ｌ（λ）は、測定自体が困難であり、さらに、波長λに応じて変化する。特に、散乱は、波長λが５００ｍ以下の短波長の光で生じやすい。従って、緑、青、紫色といった短波長の光は、散乱の影響も顕著で透過しづらくなる。そこで、波長設定部１９は、短波長を波長λの候補とする際には、演算時に特別な補正をすると好適である。 It should be noted that the equations (1) and (2) described above with reference to FIG. 7 are ideal relational equations when there is no light scattering on the surface and inside of the object, and as shown in FIG. Scattering occurs.
FIG. 8 is a schematic diagram for explaining the relationship between the absorption coefficient and transmittance of an object when scattering is considered.
FIG. 8A shows the ideal state of light transmission in the object when there is no scattering, as described in FIG.
FIG. 8B shows a state of light transmission in the object when there is scattering.
FIG. 8C shows a state of light transmission in the object when the reflected light is measured.
When there is scattering, the following equation (3) is used instead of the above equation (2) as the relationship between the absorption coefficient α (λ) of the object and the transmittance T (λ) for light of wavelength λ. It is done.

In equation (3), G (λ) represents attenuation due to scattering, l (λ) represents the optical path length in the object in the case of scattering, and n represents the total number of optical paths due to scattering. Show.
As apparent from the equation (3), when there is scattering, the thickness d is not used, and the average optical path length l (λ) is used.
However, the average optical path length l (λ) is difficult to measure and further changes according to the wavelength λ. In particular, scattering is likely to occur with short-wavelength light having a wavelength λ of 500 m or less. Accordingly, light of short wavelengths such as green, blue, and purple is not easily transmitted due to the influence of scattering. Therefore, when the wavelength setting unit 19 sets the short wavelength as a candidate for the wavelength λ, it is preferable to perform a special correction at the time of calculation.

  In addition, this invention is not limited to the above-mentioned embodiment, The deformation | transformation in the range which can achieve the objective of this invention, improvement, etc. are included in this invention.

In other words, the pulsation measuring device to which the present invention is applied only needs to have the following configuration, and can take various embodiments including the above-described embodiment.
That is, the pulsation measuring device for measuring the pulsation of a living body to which the present invention is applied,
A light emitting unit that emits light of a predetermined wavelength;
An output unit configured to receive light emitted from the light emitting unit and transmitted through a measurement target site of a living body, and to output an electrical signal corresponding to the intensity of the light;
Based on the time transition of the electrical signal output from the output unit, an acquisition unit that acquires pulsation data in the measurement target site;
With
The wavelength of the light emitting unit is set based on the thickness and absorption coefficient of the measurement target part.
Thus, the wavelength of the light emitting unit, which has not been considered in the past, is set based on the thickness of the measurement target region and the absorption coefficient. As a result, it is possible to measure the pulsation of a living organism during exercise, particularly the pulsation of a small experimental animal such as the guinea pig 51 of FIG. 3 during exercise.

  Here, in the above-described embodiment, the LED light emitting unit 13 is employed as the light emitting unit. However, the present invention is not particularly limited thereto, and the wavelength that can be set based on the thickness of the measurement target region and the absorption coefficient. Thus, a light emitting portion capable of emitting light is sufficient.

In particular,
The measurement target site is an ear of a small experimental animal,
The wavelength of the light emitting unit is set in a yellow light band,
Can be.
This makes it possible to accurately and appropriately measure the pulsation of a small experimental animal such as the guinea pig 51 in FIG. 3 during exercise.

Furthermore, the pulsation measuring device to which the present invention is applied is
A wavelength setting unit that variably sets the wavelength of the light emitting unit based on the thickness and absorption coefficient of the measurement target part,
May be further provided.
Thereby, it becomes possible to measure pulsation accurately and appropriately regardless of the difference in the measurement target region. Here, the difference in the region to be measured is not only the difference in the type of living body such as a human or a small experimental animal (the difference in ear thickness and blood flow), but also the difference in the region in the same living body (ear and Other parts such as a difference from a finger or the like) are also included.

  Here, in the above-described embodiment, the N LED light emitting units 13-1 to 13-N that emit single color lights different from each other are employed as the light emitting units in order to enable variable setting of the wavelength. However, the present invention is not particularly limited to this, and a light emitting unit capable of “variable setting of wavelength” is sufficient. Accordingly, the type of the light emitting unit is not particularly limited to the LED, and any type can be adopted, and the number of the light emitting units can be any number including one if the wavelength can be variably set. You can also.

In the above-described embodiment, the data acquisition unit 16 to the wavelength setting unit 19 in the pulsation measuring device to which the present invention is applied have been described with respect to the example provided in the computer 31, but the present invention is not particularly limited thereto.
For example, the data acquisition unit 16 to the wavelength setting unit 19 can be provided in general electronic devices having the above-described functions. Specifically, for example, the data acquisition unit 16 to the wavelength setting unit 19 are provided in a notebook personal computer, a printer, a television receiver, a video camera, a portable navigation device, a smartphone, a mobile phone, a portable game machine, and the like. Can be.

In this case, each process necessary for exhibiting each function of the data acquisition unit 16 to the wavelength setting unit 19 can be executed by hardware or can be executed by software.
In other words, the functional configurations of the data acquisition unit 16 to the wavelength setting unit 19 in FIG. 1 are merely examples, and are not particularly limited. That is, it is sufficient that the function capable of executing the above-described series of processes as a whole is provided in the pulsation measuring apparatus, and what functional blocks are used to realize this function is limited to the example of FIG. Not.
In addition, one functional block may be constituted by hardware alone, software alone, or a combination thereof.

When a series of processing is executed by software, a program constituting the software is installed on a computer or the like from a network or a recording medium.
The computer may be a computer incorporated in dedicated hardware. The computer may be a computer that can execute various functions by installing various programs, for example, the computer 31 described above.

The recording medium including such a program is not only constituted by a removable medium (not shown) distributed separately from the apparatus main body in order to provide the user with the program, but is also provided to the user in a state of being pre-installed in the apparatus main body. It is composed of a provided recording medium or the like.
The removable medium is composed of, for example, a magnetic disk (including a floppy disk), an optical disk, a magneto-optical disk, or the like. The optical disk is composed of, for example, a CD-ROM (Compact Disk-Read Only Memory), a DVD (Digital Versatile Disk), or the like. The magneto-optical disk is configured by an MD (Mini-Disk) or the like. In addition, the recording medium provided to the user in a state of being preinstalled in the apparatus main body includes, for example, a ROM (not shown) in which a program is recorded, a hard disk (not shown), and the like.

In the present specification, the step of describing the program recorded on the recording medium is not limited to the processing performed in time series along the order, but is not necessarily performed in time series, either in parallel or individually. The process to be executed is also included.
Further, in the present specification, the term “system” means an overall apparatus configured by a plurality of devices, a plurality of means, and the like.

11 ... LED drive power supply,
12 ... switching part,
DESCRIPTION OF SYMBOLS 13 ... LED light emission part 14 ... Light-receiving part 15 ... Amplifier 16 ... Data acquisition part,
17: Data display section,
18 ... thickness acquisition part,
19: Wavelength setting unit 51: Guinea pig

Claims (4)

A pulsation measuring device for measuring a pulsation of a living body,
A light emitting unit that emits light of a predetermined wavelength;
An output unit configured to receive light emitted from the light emitting unit and transmitted through a measurement target site of a living body, and to output an electrical signal corresponding to the intensity of the light;
Based on the time transition of the electrical signal output from the output unit , an acquisition unit that acquires pulsation data in the measurement target site ;
Based on the thickness and the absorption coefficient before Symbol stbm, a wavelength setting portion that sets the wavelength of the light emitting portion,
A pulsation measuring device comprising: The measurement target site is an ear of a small experimental animal,
The wavelength setting unit is set in a yellow light band as the wavelength of the light emitting unit ,
The pulsation measuring device according to claim 1. Pulsation measuring device a pulsating measuring how to measure the pulsation of a living body,
A light emitting step for emitting light of a predetermined wavelength;
An output step for receiving light emitted in the process of the light emission step and transmitted through the measurement target site of the living body, and outputting an electrical signal corresponding to the intensity of the light;
Based on the time transition of the electrical signal output in the processing of the output step , an acquisition step of acquiring pulsation data in the measurement target part ;
Based on the thickness and the absorption coefficient before Symbol stbm, and wavelength setting step of setting a wavelength of said light emitting portion,
A pulsation measuring method including : In order to measure the pulsation of the living body
A light emitting unit that emits light of a predetermined wavelength;
An output unit configured to receive light emitted from the light emitting unit and transmitted through a measurement target site of a living body, and to output an electrical signal corresponding to the intensity of the light;
A computer that executes control for measuring pulsation of a living body using a sensor comprising:
Based on the time transition of the electrical signal output from the output unit , acquisition means for acquiring pulsation data in the measurement target part ,
Based on the thickness and the absorption coefficient before Symbol stbm, and wavelength setting means for setting the wavelength of the light emitting portion,
Program to make it work .

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