JP2020188916A - Measurement apparatus - Google Patents

Abstract

To provide a technique which allows a user to accurately know the flow rate of the blood flowing in a body.SOLUTION: A measurement apparatus comprises: an irradiation device which emits first laser light and second laser light intersecting the first laser light into a body; a light-receiving device which receives the scattered light that is generated due to the contact of the intersection point between the first laser light and the second laser light emitted by the irradiation device to the blood flowing in the body and outputs a signal in accordance with the received scattered light; a display device; and a processing device. The processing device identifies the flow rate of the blood to which the intersection point contacts on the basis of the signal output by the light-receiving device and displays the identified flow rate of the blood on the display device.SELECTED DRAWING: Figure 2

Description

The techniques disclosed herein relate to measuring devices.

Patent Document 1 discloses a measuring device for measuring the flow velocity of blood flowing through the body.

Japanese Unexamined Patent Publication No. 2008-272805

With the technique of Patent Document 1, it is difficult to accurately measure the flow velocity of blood flowing through the body, and it is difficult for the user to accurately know the flow velocity of blood. Therefore, the present specification provides a technique that enables the user to accurately know the flow velocity of blood flowing through the body.

The measuring device disclosed in the present specification includes an irradiation device that irradiates a first laser beam and a second laser beam that intersects with the first laser light toward the body, and a first laser beam that is irradiated by the irradiation device. It is provided with a light receiving device, a display device, and a processing device that receive scattered light generated when the intersection of the second laser beam and the second laser light hits blood flowing in the body and outputs a signal corresponding to the received scattered light. .. The processing device specifies the flow velocity of blood hitting the intersection based on the signal output by the light receiving device, and displays the specified blood flow velocity on the display device.

According to this configuration, since the blood flow velocity is specified based on the signals corresponding to the scattered light generated by the first laser beam and the second laser beam, the blood flow velocity can be accurately specified. Further, since the flow velocity is displayed on the display device, the user of the measuring device can know the blood flow velocity with high accuracy.

The processing device may display a display representing an artery or vein on the display device when the flow rate of the specified blood is faster than a predetermined first flow rate.

The flow rate of blood flowing through arteries or veins in the body is faster than the flow rate of blood flowing through other capillaries. Therefore, when the flow velocity of the blood at the intersection of the first laser beam and the second laser beam is faster than the predetermined first flow velocity, it can be determined that the blood vessel through which the blood is flowing is an artery or a vein. .. In this case, a display representing an artery or vein is displayed on the display device. This allows the user who looks at the display device to know the position of an artery or vein in the body. For example, a doctor looking at a display device can know the position of an artery or vein of a patient.

The measuring device may further include a first blocking device that blocks the first laser beam irradiated by the irradiation device. The first blocking device may be configured to be able to switch between a blocking state that blocks the first laser light and a non-blocking state that does not block the first laser light.

According to this configuration, by switching to the blocking state in which the first laser light is blocked, it is possible to acquire a signal corresponding to the scattered light generated by the second laser light. Further, by switching to the non-blocking state in which the first laser light is not blocked, it is possible to acquire a signal corresponding to the scattered light generated by the first laser light and the second laser light. Since the signal in the blocked state and the signal in the non-blocked state can be acquired, the blood flow velocity can be accurately specified based on these signals.

The measuring device may further include a second blocking device that blocks the second laser beam irradiated by the irradiation device. The second blocking device may be configured to be switchable between a blocking state that blocks the second laser beam and a non-blocking state that does not block the second laser light. The processing device includes a signal output by the light receiving device when both the first blocking device and the second blocking device are in the non-blocking state, and the second blocking device while the first blocking device is in the blocking state. A signal output by the light receiving device when the device is in the non-blocking state and a signal output by the light receiving device when the first blocking device is in the non-blocking state while the second blocking device is in the blocking state. And, the flow velocity of the blood hitting the intersection may be specified based on.

According to this configuration, the blood flow velocity is accurately specified by specifying the blood flow velocity by combining the blocked / non-blocked state of the first blocking device and the blocked / non-blocking state of the second blocking device. can do.

The processing device is based on a signal output by the light receiving device when the first blocking device is in the non-blocking state and a signal output by the light receiving device when the first blocking device is in the blocking state. The flow velocity of the blood hitting the intersection may be specified. According to this configuration, the blood flow velocity can be accurately specified by switching between the blocked state and the non-blocked state of the first blocking device and specifying the blood flow velocity.

It is a figure which shows the schematic structure of the measuring apparatus which concerns on Example. It is a figure which shows the state which the measuring apparatus which concerns on an Example is applied to a human body. FIG. 3 is a sectional view taken along line III-III of FIG. It is a front view which shows the schematic structure of the shutoff device which concerns on embodiment. It is sectional drawing which shows the schematic structure of the light receiving device which concerns on Example. It is a side view which shows the schematic structure of the light receiving element which concerns on Example. It is a top view which shows the schematic structure of the light receiving element which concerns on Example. It is a block diagram of the measuring apparatus which concerns on Example. It is a flowchart of the measurement process which concerns on 1st Example executed by the measuring apparatus. It is a figure which shows an example of the display in the display device which concerns on Example. It is a figure which shows an example of a frequency spectrum. It is a figure which shows an example of the waveform of the flow velocity of blood flowing through the body. It is a figure which shows another example of the waveform of the flow velocity of blood flowing through the body. It is a flowchart of the measurement process which concerns on 2nd Example executed by the measuring apparatus. It is a figure which shows another example of the display in the display device which concerns on Example. It is a figure which shows another example of the display in the display device which concerns on Example. It is a figure which shows the schematic structure of the measuring apparatus which concerns on another Example. It is a figure which shows the schematic structure of the measuring apparatus which concerns on 3rd Example. It is a flowchart of the measurement process which concerns on 3rd Example executed by the measuring apparatus.

(First Example)
The measuring device 1 according to the embodiment will be described with reference to the drawings. As shown in FIGS. 1 and 2, the measuring device 1 according to the first embodiment is applied to the human body B. For example, the measuring device 1 is applied to a person's arms, legs, torso, and the like. In the examples shown in FIGS. 1 and 2, the measuring device 1 is applied to a human arm. The person to which the measuring device 1 is applied is, for example, a patient. The user of the measuring device 1 is, for example, a doctor. A plurality of blood vessels 103 exist in the body 101 of a person to which the measuring device 1 is applied, and blood flows through the plurality of blood vessels 103. The plurality of blood vessels 103 are, for example, arteries, veins or capillaries. The blood in the body 101 flows through the arteries, veins and capillaries existing in the body 101. Blood pumped from the heart flows through the arteries. Blood is flowing back to the heart in the veins. In addition, blood flowing out of arteries or blood flowing into veins flows through the capillaries. The flow velocity of blood flowing through the arteries is faster than the flow velocity of blood flowing through the veins due to the influence of the heartbeat. In addition, the flow velocity of blood flowing through veins is faster than the flow velocity of blood flowing through capillaries. In addition, the flow velocity of blood flowing through arteries and veins changes periodically due to the influence of the heartbeat. The amount of change in the flow velocity of blood flowing through the arteries is larger than the amount of change in the flow velocity of blood flowing through the veins due to the influence of the heartbeat.

The measuring device 1 includes a housing 8, an irradiation device 2, a blocking device 5, a light receiving device 3, a display device 4, and a processing device 9. The irradiation device 2, the blocking device 5, and the light receiving device 3 are arranged inside the housing 8 and are housed in the housing 8. The display device 4 and the processing device 9 are arranged outside the housing 8. In another embodiment, the display device 4 and the processing device 9 may be arranged inside the housing 8. The housing 8 includes a main body member 80 and a tip member 81. The main body member 80 is a portion gripped by the user of the measuring device 1. The tip member 81 is a portion that is pressed against the surface 102 (skin) of the human body B when the measuring device 1 is applied to the human body B. The end face of the tip member 81 is in close contact with the surface 102 of the human body B. The tip member 81 is a thin plate-shaped member.

As shown in FIG. 3, an opening 82 is formed in the tip member 81 of the housing 8. The opening 82 is formed in a quadrangular shape. Further, the tip member 81 includes a plurality of protrusions 85. Protrusions 85 are formed on each of the four sides of the opening 82. Each protrusion 85 is formed at the center of each side of the opening 82. Each protrusion 85 projects from the peripheral edge of the opening 82 toward the center. Each protrusion 85 is tapered from the peripheral portion of the opening 82 toward the central portion. Each protrusion 85 is formed in a triangular shape.

As shown in FIGS. 1 and 2, the irradiation device 2 arranged inside the housing 8 is a device that irradiates the first laser light L1 and the second laser light L2 toward the human body 101. .. The first laser beam L1 and the second laser beam L2 intersect with each other. The point where the first laser beam L1 and the second laser beam L2 intersect is called an intersection 10. The first laser beam L1 and the second laser beam L2 pass through the opening 82 of the housing 8.

The irradiation device 2 includes a light emitting element 21, a collimator lens 22, a diffraction grating 23, a moving device 25, a first mirror 43, and a second mirror 44. The light emitting element 21 is, for example, a laser diode (LD). The light emitting element 21 is arranged so as to face the collimator lens 22. The light emitting element 21 emits laser light L toward the collimator lens 22. The laser beam L emitted by the light emitting element 21 is incident on the collimator lens 22. The light emitting element 21 is arranged between the diffraction grating 23 and the first mirror 43 and the second mirror 44. The light emitting element 21 emits the laser beam L on the side opposite to the direction in which the first mirror 43 and the second mirror 44 are arranged. The laser light L is, for example, near-infrared light having a wavelength of about 850 nm-1300 nm.

The collimator lens 22 is arranged between the light emitting element 21 and the diffraction grating 23. The collimator lens 22 emits the laser light L emitted by the light emitting element 21 as parallel light. The laser light L (parallel light) emitted from the collimator lens 22 is incident on the diffraction grating 23.

The diffraction grating 23 is a device that splits the laser light L incident on the diffraction grating 23 into the first laser light L1 and the second laser light L2 by utilizing the diffraction of light. The diffraction grating 23 is a reflection type diffraction grating. When the laser light L incident on the diffraction grating 23 is reflected by the diffraction grating 23, it is divided into a first laser light L1 and a second laser light L2. The first laser light L1 and the second laser light L2 generated by the diffraction grating 23 travel in different directions. The first laser beam L1 and the second laser beam L2 travel so as to be line-symmetric with respect to the line connecting the light emitting element 21 and the collimator lens 22. In the examples shown in FIGS. 1 and 2, the first laser beam L1 travels diagonally upward to the right, and the second laser beam L2 travels diagonally upward to the left. The first laser light L1 travels toward the first mirror 43, and the second laser light L2 travels toward the second mirror 44. The wavelength of the first laser beam L1 and the wavelength of the second laser beam L2 are the same wavelength. Further, the frequency of the first laser beam L1 and the frequency of the second laser beam L2 are the same frequency.

The moving device 25 is a device that moves the diffraction grating 23. The diffraction grating 23 is movable. The moving device 25 is, for example, a mechanical device, and the user (for example, a doctor) of the measuring device 1 can move the diffraction grating 23 in the vertical direction of FIG. 1 by turning the bolt 251. The moving device 25 may be manual or automatic. By moving the diffraction grating 23 by the moving device 25, the irradiation positions of the first laser light L1 and the second laser light L2 can be moved. The moving device 25 can move the position of the intersection 10 between the first laser light L1 and the second laser light L2 by moving the irradiation positions of the first laser light L1 and the second laser light L2. Further, the moving device 25 includes a linear encoder 252. The linear encoder 252 is a device for measuring a moving distance. The moving device 25 can specify the distance at which the intersection 10 is moved by the linear encoder 252. The moving device 25 transmits information on the distance traveled by the intersection 10 to the processing device 9.

The first mirror 43 and the second mirror 44 are arranged between the diffraction grating 23 and the human body B. The first mirror 43 and the second mirror 44 face each other. The first mirror 43 includes a first reflecting surface 241. Further, the second mirror 44 includes a second reflecting surface 242. The first reflecting surface 241 and the second reflecting surface 242 face each other. The first laser beam L1 generated by the diffraction grating 23 is incident on the first reflecting surface 241 of the first mirror 43. The first laser beam L1 is reflected by the first reflecting surface 241. Further, the second laser beam L2 generated by the diffraction grating 23 is incident on the second reflecting surface 242 of the second mirror 44. The second laser beam L2 is reflected by the second reflecting surface 242.

The first laser beam L1 reflected by the first mirror 43 travels in the first direction D1. The second laser beam L2 reflected by the second mirror 44 travels in the second direction D2. The first laser beam L1 and the second laser beam L2 pass through the opening 82 of the tip member 81 of the housing 8 and are emitted from the housing 8. The first laser beam L1 and the second laser beam L2 emitted from the housing 8 are incident on the human body 101. The first direction D1 and the second direction D2 are directions that intersect each other. The first laser beam L1 traveling in the first direction D1 and the second laser beam L2 traveling in the second direction D2 intersect at an intersection 10. The first laser beam L1 and the second laser beam L2 overlap each other and interfere with each other.

When the intersection 10 of the first laser light L1 and the second laser light L2 hits the blood flowing through the human body 101, the first laser light L1 and the second laser light L2 are scattered. More specifically, the first laser beam L1 and the second laser beam L2 are scattered by hitting particles (for example, red blood cells) contained in blood. The first laser beam L1 and the second laser beam L2 hit blood from different directions. The first laser beam L1 travels in the first direction D1 and hits the blood. The second laser beam L2 travels in the second direction D2 and hits the blood. Scattered light is generated when the first laser light L1 and the second laser light L2 hit the blood flowing through the body 101. Scattered light is generated by scattering the first laser light L1 and the second laser light L2. When the first laser beam L1 and the second laser beam L2 hit the blood and scatter, the frequencies of the laser beams L1 and L2 change due to the Doppler shift. The frequency of the scattered light generated by the scattering of the laser lights L1 and L2 is different from the frequency of each of the laser lights L1 and L2.

The scattered light generated by the scattering of the laser lights L1 and L2 travels in various directions. Of the scattered light generated by the scattering of the laser beams L1 and L2, the light receiving device 3 receives the scattered light P traveling toward the light receiving device 3. The scattered light P is interference light in which the scattered light generated by the scattering of the first laser light L1 and the scattered light generated by the scattering of the second laser light L2 interfere with each other and overlap each other. The scattered light P is incident on the light receiving device 3.

A blocking device 5 is arranged between the first mirror 43 of the irradiation device 2 and the tip member 81 of the housing 8. The blocking device 5 is arranged on the path of the first laser beam L1. As shown in FIG. 4, the blocking device 5 includes a frame member 51 and an opening / closing member 52. An opening 53 is formed in the frame member 51. The frame member 51 is arranged so that the opening 53 is located on the path of the first laser beam L1 (see FIGS. 1 and 2). The opening / closing member 52 opens / closes the opening 53 of the frame member 51. When the opening / closing member 52 is in the closed state, the first laser beam L1 does not pass through the opening 53. The opening / closing member 52 blocks the first laser beam L1. On the other hand, when the opening / closing member 52 is in the open state, the first laser beam L1 passes through the opening 53. The opening / closing member 52 does not block the first laser beam L1.

The blocking device 5 is configured to be able to switch between the closed state and the open state of the opening / closing member 52. That is, the blocking device 5 is configured to be able to switch between a blocking state that blocks the first laser light L1 and a non-blocking state that does not block the first laser light L1. When the blocking device 5 is in the blocking state, the first laser beam L1 is not applied to the human body B, and the first laser beam L1 is not incident on the human body 101. On the other hand, when the blocking device 5 is in the non-blocking state, the first laser beam L1 is irradiated to the human body B, and the first laser beam L1 is incident on the human body 101.

The light receiving device 3 that receives the scattered light P is arranged between the human body B and the irradiating device 2. The light receiving device 3 is fixed to the irradiation device 2 by a fixture (not shown). The light receiving device 3 is arranged so as to face the human body B. As shown in FIG. 5, the light receiving device 3 includes a light receiving element 31 and a light-shielding box body 38. The light receiving element 31 is, for example, a photodiode (PD). The light receiving element 31 is arranged in the box body 38.

The box body 38 includes a front wall 38a, a rear wall 38b, and a pair of side walls 38c and 38c. In a state where the measuring device 1 is applied to the human body B (not shown in FIG. 5), the front wall 38a is arranged between the human body B and the light receiving element 31. The rear wall 38b is arranged between the light receiving element 31 and the irradiation device 2 (not shown in FIG. 5). The pair of side walls 38c, 38c are arranged between the front wall 38a and the rear wall 38b. The light receiving element 31 is fixed to the rear wall 38b of the box body 38. The front wall 38a of the box body 38 is arranged at a position away from the light receiving element 31. A hollow light passing hole 35 is formed in the front wall 38a.

The light passing hole 35 extends in a direction toward the light receiving element 31 (vertical direction in FIG. 5). The light passage hole 35 includes an entrance port 36 and an exit port 37. The scattered light P generated by the scattering of the laser lights L1 and L2 is incident on the light passing hole 35 from the incident port 36. The scattered light P traveling toward the light receiving device 3 is incident on the light passing hole 35. The scattered light P incident on the light passing hole 35 passes through the light passing hole 35 and is emitted from the exit port 37. The scattered light P emitted from the exit port 37 is incident on the light receiving element 31.

As shown in FIGS. 6 and 7, the light receiving element 31 includes an effective light receiving region 312 and a light receiving surface 313. The effective light receiving region 312 is formed in the central portion of the light receiving element 31. The effective light receiving region 312 is a region in which incident light can be converted into an electric signal. The light receiving element 31 can effectively receive the scattered light P incident on the effective light receiving region 312. The light receiving surface 313 is the surface of the effective light receiving region 312. The light receiving element 31 can receive the scattered light P incident on the light receiving surface 313. When the light receiving element 31 receives the scattered light P, it outputs an electric signal corresponding to the intensity of the scattered light P. In this embodiment, the light receiving element 31 outputs a voltage signal according to the intensity of the scattered light P.

As shown in FIG. 8, the processing device 9 is electrically connected to the light emitting element 21 of the irradiation device 2 and the light receiving element 31 of the light receiving device 3. The processing device 9 calculates the flow velocity of blood flowing through the human body 101 based on the laser light L emitted by the light emitting element 21 and the scattered light P received by the light receiving element 31. The processing device 9 calculates the blood flow rate by a calculation method based on the Doppler shift. More specifically, the processing apparatus 9 calculates the speed of particles (eg, red blood cells) contained in blood. The method of calculating the blood flow velocity will be described later.

Further, the processing device 9 is electrically connected to the moving device 25 and the display device 4. The processing device 9 specifies the distance that the moving device 25 has moved the diffraction grating 23 based on the information received from the moving device 25. That is, the processing device 9 specifies the distance at which the moving device 25 has moved the intersection 10 between the first laser light L1 and the second laser light L2. The display device 4 is, for example, a liquid crystal monitor. The display device 4 displays, for example, the flow velocity of blood flowing through the human body 101, the distance traveled by the intersection 10, and the like. The information processing executed by the processing device 9 will be described later. Further, the processing device 9 is connected to the blocking device 5. The processing device 9 controls the operation of the blocking device 5.

Next, a method of measuring the position of a blood vessel (artery or vein) of 101 in the human body by using the above-mentioned measuring device 1 will be described. In this method, first, a user (for example, a doctor) of the measuring device 1 sets the position of the intersection 10 between the first laser beam L1 and the second laser beam L2 at the opening 82 formed in the tip member 81 of the housing 8. Placed inside (see FIG. 1). Specifically, the user manually operates the moving device 25 to move the position of the intersection 10. The user operates the moving device 25 so that the position of the intersection 10 is arranged in the opening 82 of the tip member 81. The user arranges the intersection 10 in the opening 82 with reference to the positions of the plurality of protrusions 85.

Subsequently, the user applies the measuring device 1 to the body B of a person (for example, a patient). When the user applies the measuring device 1 to the human body B, the tip member 81 of the housing 8 of the measuring device 1 is brought into close contact with the surface 102 of the human body B (see FIG. 2). As a result, the position of the opening 82 formed in the tip member 81 coincides with the position of the surface 102 of the human body B. As a result, it can be considered that the position of the intersection 10 arranged in the opening 82 coincides with the position of the surface 102 of the human body B. The processing device 9 recognizes the distance X when the position of the intersection 10 coincides with the position of the surface 102 of the human body B as 0 (zero).

Subsequently, the user manually operates the moving device 25 to move the intersection 10 from the surface 102 of the human body B toward the deep part of the human body 101. The intersection 10 may be moved from the surface 102 of the human body B to the deep part of the human body 101 by the automatic operation of the moving device 25. By the operation of the moving device 25, the intersection 10 enters the human body 101. The moving device 25 transmits information on the distance X at which the intersection 10 has been moved to the processing device 9.

When the intersection 10 that has entered the human body 101 hits the blood flowing through the human body 101, the first laser beam L1 and the second laser beam L2 are scattered. Scattered light P is generated by scattering the first laser light L1 and the second laser light L2. The scattered light P generated by the scattering of the laser lights L1 and L2 travels toward the light receiving device 3 and is incident on the light receiving device 3. The light receiving element 31 of the light receiving device 3 receives the scattered light P. The light receiving element 31 outputs a signal corresponding to the received scattered light P. In this embodiment, the light receiving element 31 outputs a voltage signal according to the intensity of the scattered light P. The processing device 9 receives the voltage signal output by the light receiving element 31.

Next, the measurement process executed by the above-mentioned measuring device 1 will be described. The measurement process is executed, for example, when the power of the measuring device 1 is turned on. As shown in FIG. 9, in the measurement process S11, the processing device 9 receives the information of the distance X from the moving device 25. Subsequently, in S13, the processing device 9 identifies the distance X to which the moving device 25 has moved the intersection 10 based on the information of the distance X received from the moving device 25. That is, the processing device 9 identifies the distance X at which the intersection 10 has moved from the surface 102 of the human body B to the body 101 by the operation of the moving device 25. Subsequently, in S15, the processing device 9 displays the specified distance X on the display device 4 (see FIG. 10). The distance X between the surface 102 of the human body B and the intersection 10 that has entered the body 101 is displayed on the display device 4.

Subsequently, in S17, the processing device 9 receives the voltage signal from the light receiving element 31. The processing device 9 samples the voltage signal received from the light receiving element 31 at intervals of, for example, 0.06 seconds. Subsequently, in S19, the processing device 9 Fourier transforms the voltage signal received from the light receiving element 31 and sampled. The processing device 9 can execute the Fourier transform by, for example, an FFT (Fast Fourier Transform) analyzer. The Fourier transform is a technique that can transform a function of time into a function of frequency. Since the Fourier transform is well known, detailed description thereof will be omitted. The processing device 9 performs a Fourier transform to generate a frequency spectrum. Further, the processing device 9 converts the generated frequency spectrum into decibels. The frequency spectrum converted to decibels is shown in relation to the frequency and the voltage level, for example, as shown in FIG.

Subsequently, in S21, the processing device 9 detects the peak frequency fp in the frequency spectrum obtained in the processing of S19. The peak frequency fp is the frequency corresponding to the most prominent voltage level in the frequency spectrum. Further, the frequency in the vicinity thereof may be set as the peak frequency fp. Subsequently, in S23, the processing device 9 identifies the blood flow rate based on the peak frequency fp in the frequency spectrum. The processing device 9 can calculate the blood flow velocity by the following formula (1). However, in the following formula (1), v is the flow velocity of blood flowing through the human body 101. Further, λ is the wavelength of the first laser light L1 and the second laser light L2. Further, θ is an angle of 1/2 of the intersection angle of the first laser beam L1 and the second laser beam L2 (see FIGS. 1 and 2). The processing apparatus 9 can specify the flow velocity of blood hit by the intersection 10 of the first laser light L1 and the second laser light L2 by the following formula (1). The processing device 9 may specify the blood flow rate by another calculation method. The calculation method is not particularly limited.

Subsequently, in S25, the processing device 9 determines whether or not the flow velocity of the blood specified in S23 above is faster than the predetermined first flow velocity. The predetermined first flow velocity is determined with reference to, for example, the flow velocity of blood flowing through a general artery or vein. The predetermined first flow velocity is, for example, 50 mm / s. If the processing device 9 makes an affirmative decision in S25 (Yes in S25), the processing device 9 proceeds to S27. On the other hand, when the processing device 9 makes a negative determination in S25 (No in S25), the processing device 9 proceeds to S31.

The flow velocity of blood flowing through the arteries or veins of 101 in the human body is faster than the flow velocity of blood flowing through the capillaries. When the processing device 9 makes an affirmative judgment in S25, it can be determined that the blood vessel through which the blood is flowing is an artery or a vein because the flow velocity of the blood hitting the intersection 10 is faster than the predetermined first flow velocity. .. On the other hand, when the processing device 9 makes a negative judgment in S25, the flow velocity of the blood hitting the intersection 10 is slower than the predetermined first flow velocity, so that the blood vessel through which the blood flows is not an artery or a vein (capillaries). ) Can be judged. Alternatively, when the processing device 9 makes a negative judgment in S25, it can be considered that the blood vessel does not exist at the position of the intersection 10.

In S31 after making a negative determination in S25, the processing device 9 displays a display representing the capillaries on the display device 4 (see FIG. 10). Alternatively, the processing device 9 displays on the display device 4 a display indicating that the blood vessel does not exist (see FIG. 10). For example, the processing device 9 displays the character string C3 of "capillaries or none" on the display device 4. Further, the processing device 9 displays the character string C3 next to the distance X specified in S13 and displayed in S15. For example, when the distance X specified in S13 and displayed in S15 is 0.5 mm, the processing device 9 displays the character string C3 next to the distance X (0.5 mm). Further, in S31, the processing device 9 displays the blood flow velocity specified in S23 above on the display device 4 (see FIG. 10). The processing device 9 displays the flow velocity (for example, 30 mm / s) next to the character string C3 corresponding to the distance X displayed in S15. The processing device 9 returns to the above-mentioned S11 after the processing of S31 is completed.

In S27 after making an affirmative decision in S25, the processing device 9 determines whether or not the flow velocity of the blood specified in S23 above is faster than the predetermined second flow velocity. The predetermined second flow velocity is determined with reference to, for example, the flow velocity of blood flowing through a general artery or vein. The predetermined second flow velocity is a flow velocity faster than the above-mentioned predetermined first flow velocity. The predetermined second flow velocity is, for example, 300 mm / s. If the processing device 9 makes an affirmative decision in S27 (Yes in S27), the processing device 9 proceeds to S29. On the other hand, when the processing device 9 makes a negative determination in S27 (No in S27), the processing device 9 proceeds to S33.

The flow velocity of blood flowing through the arteries of 101 in the human body is faster than the flow velocity of blood flowing through veins. When the processing device 9 makes an affirmative judgment in S27, it can be determined that the blood vessel through which the blood is flowing is an artery because the flow velocity of the blood hitting the intersection 10 is faster than the predetermined second flow velocity. On the other hand, when the processing device 9 makes a negative judgment in S27, it can be determined that the blood vessel through which the blood is flowing is a vein because the flow velocity of the blood hitting the intersection 10 is slower than the predetermined second flow velocity. ..

In S29 after making an affirmative decision in S27, the processing device 9 displays a display representing the artery on the display device 4 (see FIG. 10). For example, the processing device 9 displays the character string C1 of the “artery” representing the artery on the display device 4. Further, the processing device 9 displays a display representing an artery next to the distance X specified in S13 and displayed in S15. For example, when the distance X specified in S13 and displayed in S15 is 8.0 mm, the processing device 9 displays the character string C1 next to the distance X (8.0 mm). Further, in S29, the processing device 9 displays the blood flow velocity specified in S23 above on the display device 4 (see FIG. 10). The processing device 9 displays the flow velocity (for example, 400 mm / s) next to the character string C1 corresponding to the distance X displayed in S15. The processing device 9 returns to the above-mentioned S11 after the processing of S29 is completed.

In S33 after the negative determination in S27, the processing device 9 displays a display indicating the vein on the display device 4 (see FIG. 10). For example, the processing device 9 displays the character string C2 of "vein" representing a vein on the display device 4. Further, the processing device 9 displays a display representing a vein next to the distance X specified in S13 and displayed in S15. For example, when the distance X specified in S13 and displayed in S15 is 5.0 mm, the processing device 9 displays the character string C2 next to the distance X (5.0 mm). Further, in S33, the processing device 9 displays the blood flow velocity specified in S23 above on the display device 4 (see FIG. 10). The processing device 9 displays the flow velocity (for example, 150 mm / s) next to the character string C2 corresponding to the distance X displayed in S15. The processing device 9 returns to the above-mentioned S11 after the processing of S33 is completed.

The processing device 9 repeats the above measurement process (S11-S33). The processing device 9 executes the above measurement process (S11-S33) for each distance X in which the moving device 25 has moved the intersection 10. Therefore, the processing device 9 specifies the type of blood vessel (artery, vein, capillary, or none) through which the blood that the intersection 10 hits is flowing, for each distance X that the moving device 25 moves the intersection 10. To do. After that, for example, when the power of the measuring device 1 is turned off, the measurement process ends.

In the above measurement process, the processing device 9 may open / close the opening / closing member 52 of the blocking device 5 when specifying the blood flow rate. More specifically, first, the processing device 9 opens the opening / closing member 52. That is, the processing device 9 puts the blocking device 5 in the non-blocking state. Then, the first laser light L1 and the second laser light L2 are incident on the human body 101 to generate scattered light P by the first laser light L1 and the second laser light L2. The light receiving element 31 receives the scattered light P. The light receiving element 31 outputs a signal corresponding to the received scattered light P. The processing device 9 receives the signal. Therefore, the processing device 9 receives the signal based on the scattered light P generated by the first laser light L1 and the second laser light L2.

Subsequently, the processing device 9 closes the opening / closing member 52. That is, the processing device 9 puts the blocking device 5 in the blocking state. Then, the first laser beam L1 is blocked. Therefore, only the second laser light L2 is incident on the human body 101, and scattered light P'is generated only by the second laser light L2. The light receiving element 31 receives the scattered light P'. The light receiving element 31 outputs a signal corresponding to the received scattered light P'. The processing device 9 receives the signal. Therefore, the processing device 9 receives the signal based on the scattered light P'generated only by the second laser light L2.

The processing device 9 can specify the blood flow velocity based on the signals P and P'received from the light receiving element 31. For example, the processing device 9 has a blood flow velocity based on the difference between the frequency spectrum based on the signal P when the blocking device 5 is in the non-blocking state and the frequency spectrum based on the signal P'when the blocking device 5 is in the blocking state. May be specified. The calculation method for specifying the blood flow rate is not particularly limited.

The measuring device 1 according to the first embodiment has been described above. As is clear from the above description, in the measuring device 1, the irradiating device 2 irradiates the first laser light L1 and the second laser light L2 intersecting the first laser light L1 toward the human body 101. .. Further, the light receiving device 3 receives the scattered light P generated by the intersection 10 of the first laser light L1 and the second laser light L2 irradiated by the irradiating device 2 hitting the blood flowing through the human body 101. The light receiving device 3 may receive the scattered light P'. The light receiving device 3 outputs a signal corresponding to the received scattered light P. The light receiving device 3 may output a signal corresponding to the scattered light P'. The processing device 9 identifies the flow velocity of the blood hit by the intersection 10 based on the signal output by the light receiving device 3 (S23), and displays the specified blood flow velocity on the display device 4 (S29, S31, S33). ..

According to this configuration, since the blood flow velocity is specified based on the signal corresponding to the scattered light P generated by the first laser light L1 and the second laser light L2, the blood flow velocity can be specified accurately. Further, since the flow velocity is displayed on the display device 4, the user of the measuring device 1 can know the blood flow velocity with high accuracy.

Further, in the above-mentioned measuring device 1, when the processing device 9 has a flow velocity of the specified blood faster than the predetermined first flow velocity (Yes in S25), the display device 4 displays a display indicating an artery or a vein (S29). , S33). According to this configuration, when the flow velocity of the blood hitting the intersection 10 of the first laser beam L1 and the second laser beam L2 is faster than the predetermined first flow velocity, the blood vessel through which the blood flows is an artery or a vein. It can be judged that there is. Therefore, in this case, a display representing an artery or a vein is displayed on the display device 4. As a result, the user who looks at the display device 4 can know the position of the artery or vein in the body 101.

In addition, the measuring device 1 includes a blocking device 5 that blocks the first laser beam L1 irradiated by the irradiating device 2. The blocking device 5 is configured to be able to switch between a blocking state in which the first laser beam L1 is blocked and a non-blocking state in which the first laser beam L1 is not blocked. According to this configuration, the processing device 9 switches the blocking device 5 to the blocking state, so that a signal based on the scattered light P'generated only by the second laser light L2 can be acquired. Further, when the processing device 9 switches the blocking device 5 to the non-blocking state, it is possible to acquire a signal based on the scattered light P generated by the first laser light L1 and the second laser light L2. Since the processing device 9 can acquire signals based on the scattered light P and P', the blood flow velocity can be accurately specified based on those signals.

Although one embodiment has been described above, the specific embodiment is not limited to the above embodiment. In the following description, the same components as those in the above description will be designated by the same reference numerals and description thereof will be omitted.

(Second Example)
In the measuring device 1 according to the second embodiment, when the processing device 9 specifies the blood flow rate in S23, the blood flow rate is specified over a predetermined time. The predetermined time is, for example, 4 seconds. This gives a waveform of blood flow velocity over a predetermined time (eg 4 seconds), for example as shown in FIG. 12 or FIG.

Further, in the measuring device 1 according to the second embodiment, as shown in FIG. 14, the processing device 9 executes the process of S47 after making an affirmative decision in S25. In S47, the processing device 9 determines whether or not the amount of change in the blood flow velocity over the predetermined time specified in S23 is larger than the predetermined amount of change. The predetermined amount of change in blood flow rate is, for example, 300 mm / s. In the example shown in FIG. 12, the blood flow velocity changes from 100 mm / s or less to 400 mm / s or more during a predetermined time (for example, 4 seconds). Therefore, the amount of change in blood flow velocity is larger than the predetermined amount of change (for example, 300 mm / s). In the example shown in FIG. 13, the blood flow velocity changes at 200 mm / s or less during a predetermined time (for example, 4 seconds). Therefore, the amount of change in blood flow velocity is smaller than the predetermined amount of change (for example, 300 mm / s). If the processing device 9 makes an affirmative decision in S47 (Yes in S47), the processing device 9 proceeds to S29. On the other hand, when the processing device 9 makes a negative determination in S47 (No in S47), the processing device 9 proceeds to S33.

The amount of change in the flow velocity of blood flowing through the arteries in the human body 101 is larger than the amount of change in the flow velocity of blood flowing through the veins. When the processing device 9 makes an affirmative judgment in S47, it can be determined that the blood vessel through which the blood is flowing is an artery because the amount of change in the blood flow velocity is larger than the predetermined amount of change. On the other hand, when the processing device 9 makes a negative determination in S47, it can be determined that the blood vessel through which the blood is flowing is a vein because the amount of change in the blood flow velocity is smaller than the predetermined amount of change.

(Other Examples)
Another example of the process in which the processing device 9 determines the amount of change in the blood flow rate in S47 will be described. In another example, as shown in FIG. 12 or 13, the processing apparatus 9 equally divides one wavelength of the blood flow velocity waveform obtained in S23 at the same time. For example, the processing device 9 divides one wavelength of the waveform into three equal parts at intervals of 0.5 seconds. Subsequently, the processing device 9 calculates the areas S1, S2, and S3 of each section of the divided waveform. The area of the waveform corresponds to the distance. Subsequently, the processing device 9 calculates the average area Sa (= S1 + S2 + S3 / 3) of the areas S1, S2, and S3 of each section. Subsequently, the processing apparatus 9 calculates the average flow velocity Va (= Sa / T) by dividing the average area Sa by the period T of one wavelength. Then, in the processing device 9, both a blood flow velocity faster than the average flow velocity Va + (plus) 100 mm / s and a blood flow velocity slower than the average flow velocity Va- (minus) 100 mm / s appear in one wavelength of the waveform. If so, it is determined that the amount of change in blood flow velocity is larger than the predetermined amount of change. The method of calculating the amount of change in blood flow velocity is not particularly limited.

In the above embodiment, the measuring device 1 is applied to the human body B, but in other embodiments, the measuring device 1 may be applied to the body of an animal other than a human (for example, a dog or a cat).

In the above embodiment, the processing device 9 executes the processing of S31, but in other embodiments, the processing of S31 may be omitted. If the processing device 9 makes a negative determination in S25, the processing device 9 may return to S11 without executing the processing of S31.

Further, the display on the display device 4 is not limited to the above configuration. For example, as shown in FIG. 15, the processing device 9 may display the range of the distance X on the display device 4. The processing device 9 displays the range of the distance X on the display device 4 after repeating the measurement process (S11-S33) a plurality of times. Further, the character string C1 of "artery" representing an artery and the character string C2 of "vein" representing a vein are displayed next to the range of the distance X.

Further, as shown in FIG. 16, the processing device 9 may display the scale of the distance X on the display device 4. Moreover, the display representing arteries and veins is not limited to character strings. For example, as shown in FIG. 16, the display representing the artery may be a dark color display, and the display representing the vein may be a light color display. Alternatively, the display representing the artery may be a display of strong light, and the display representing the vein may be a display of weak light. The display is not particularly limited as long as it can recognize arteries and veins.

In the above embodiment, the signal output from the light receiving device 3 is a voltage signal, but the present invention is not limited to this configuration, and a current signal may be output from the light receiving device 3.

In the above embodiment, the first mirror 43 and the second mirror 44 are used, but the present invention is not limited to this configuration, and instead of the mirror, all the laser light such as a glass block whose end face is sufficiently polished is used. A reflective member may be used.

In the above embodiment, the reflection type diffraction grating 23 has been used, but the present invention is not limited to this configuration, and a transmission type diffraction grating may be used instead of the reflection type. In this case, the order in which the light emitting element 21, the collimator lens 22, and the transmission type diffraction grating are arranged is opposite to the order shown in FIG. 1 (not shown). Further, the configuration of the moving device is not particularly limited as long as the irradiation positions of the first laser light L1 and the second laser light L2 can be moved to move the position of the intersection 10. Further, the first laser beam L1 and the second laser beam L2 may be generated by an element such as a beam splitter that splits the luminous flux instead of the diffraction grating 23.

In the above embodiment, the light passing hole 35 formed in the front wall 38a of the box body 38 has a hollow structure, but the present invention is not limited to this structure, and the light passing hole 35 is provided with light transmission. The member to have may be arranged. For example, the light passage hole 35 may be filled with glass.

In the above embodiment, the irradiation device 2 is provided with the moving device 25, but in other embodiments, the irradiation device 2 may not be provided with the moving device 25. In this case, the intersection 10 of the first laser beam L1 and the second laser beam L2 is located outside the housing 8 from the beginning (see FIG. 2).

In the above embodiment, the blocking device 5 is configured to include the frame member 51 and the opening / closing member 52, but the configuration of the blocking device 5 is not limited to this. In another embodiment, the first mirror 43 may constitute the blocking device 5. More specifically, as shown in FIG. 17, the first mirror 43 may include a first reflecting surface 241 and a first non-reflecting surface 243. The first reflecting surface 241 and the first non-reflecting surface 243 face in opposite directions. The first mirror 43 is rotatably configured, and can switch between a reflective state in which the first reflecting surface 241 faces the light receiving device 3 side and a non-reflective state in which the first non-reflective surface 243 faces the light receiving device 3 side. It is configured in. In the reflected state, the first laser beam L1 is reflected by the first mirror 43 and is incident on the human body 101. The first laser beam L1 is not blocked in the reflected state. The reflection state of the first mirror 43 corresponds to the non-blocking state of the blocking device 5. On the other hand, in the non-reflective state, the first laser beam L1 is not reflected by the first mirror 43 and does not enter the human body 101. In the non-reflective state, the first laser beam L1 is blocked. The non-reflective state of the first mirror 43 corresponds to the cutoff state of the blocking device 5.

(Third Example)
In the above embodiment, the blocking device 5 is arranged on the path of the first laser beam L1, but in the third embodiment, as shown in FIG. 18, the path of the first laser beam L1 and the second laser A blocking device 5 (5a, 5b) may be arranged in each of the paths of the light L2. The first blocking device 5a may be arranged on the path of the first laser beam L1, and the second blocking device 5b may be arranged on the path of the second laser beam L2. The processing device 9 has a blocked state / non-blocked state of the first blocking device 5a on the path of the first laser beam L1 and a blocked / non-blocked state of the second blocking device 5b on the path of the second laser light L2. May be switched alternately.

Next, the measurement process according to the third embodiment will be described. As shown in FIG. 19, in the measurement process according to the third embodiment, the process of S51 is executed after the process of S15. Since the processes up to S15 are the same as the processes up to S15 described in the first embodiment (see FIG. 9), detailed description thereof will be omitted. In S51 following S15, the processing device 9 puts the first blocking device 5a arranged on the path of the first laser beam L1 into a non-blocking state. Further, the processing device 9 puts the second blocking device 5b arranged on the path of the second laser beam L2 into a non-blocking state. When the processing device 9 sets both the first blocking device 5a and the second blocking device 5b in a non-blocking state, both the first laser light L1 and the second laser light L2 are irradiated to the human body B, and the first laser light L1 and Both of the second laser light L2 are incident on the human body 101.

Subsequently, in S17a, the processing device 9 receives the voltage signal from the light receiving element 31. The processing device 9 receives a voltage signal when both the first laser light L1 and the second laser light L2 are irradiating the human body B. Since the process of S17a is the same as the process of S17 described in the first embodiment (see FIG. 9), detailed description thereof will be omitted. Subsequently, in S19a, the processing device 9 Fourier transforms the voltage signal received from the light receiving element 31 and sampled. Since the process of S19a is the same as the process of S19 described in the first embodiment (see FIG. 9), detailed description thereof will be omitted.

Subsequently, in S21a, the processing device 9 detects the peak frequency fp (first peak frequency fp1) in the frequency spectrum obtained by the processing of S19a. Since the process of S21a is the same as the process of S21 described in the first embodiment (see FIG. 9), detailed description thereof will be omitted.

Subsequently, in S52, the processing device 9 puts the first blocking device 5a arranged on the path of the first laser beam L1 into a non-blocking state. On the other hand, the processing device 9 puts the second blocking device 5b arranged on the path of the second laser beam L2 into a blocking state. When the processing device 9 puts the first blocking device 5a in a non-blocking state, the first laser beam L1 is irradiated to the human body B, and the first laser beam L1 is incident on the human body 101. On the other hand, when the processing device 9 puts the second blocking device 5b in the blocking state, the second laser beam L2 is not irradiated to the human body B, and the second laser beam L2 is not incident on the human body 101.

Subsequently, in S17b, the processing device 9 receives the voltage signal from the light receiving element 31. The processing device 9 receives a voltage signal when the first laser beam L1 is irradiating the human body B while the second laser beam L2 is not irradiating the human body B. Since the process of S17b is the same as the process of S17 described in the first embodiment (see FIG. 9), detailed description thereof will be omitted. Subsequently, in S19b, the processing device 9 Fourier transforms the voltage signal received from the light receiving element 31 and sampled. Since the process of S19b is the same as the process of S19 described in the first embodiment (see FIG. 9), detailed description thereof will be omitted.

Subsequently, in S21b, the processing device 9 detects the peak frequency fp (second peak frequency fp2) in the frequency spectrum obtained by the processing of S19b. Since the process of S21b is the same as the process of S21 described in the first embodiment (see FIG. 9), detailed description thereof will be omitted.

Subsequently, in S53, the processing device 9 sets the first blocking device 5a arranged on the path of the first laser beam L1 in a blocking state. On the other hand, the processing device 9 puts the second blocking device 5b arranged on the path of the second laser beam L2 into a non-blocking state. When the processing device 9 sets the first blocking device 5a in the blocking state, the first laser light L1 is not irradiated to the human body B, and the first laser light L1 is not incident on the human body 101. On the other hand, when the processing device 9 puts the second blocking device 5b in a non-blocking state, the second laser beam L2 is irradiated to the human body B, and the second laser beam L2 is incident on the human body 101.

Subsequently, in S17c, the processing device 9 receives the voltage signal from the light receiving element 31. The processing device 9 receives a voltage signal when the first laser beam L1 is not irradiating the human body B while the second laser beam L2 is irradiating the human body B. Since the process of S17c is the same as the process of S17 described in the first embodiment (see FIG. 9), detailed description thereof will be omitted. Subsequently, in S19c, the processing device 9 Fourier transforms the voltage signal received from the light receiving element 31 and sampled. Since the process of S19c is the same as the process of S19 described in the first embodiment (see FIG. 9), detailed description thereof will be omitted.

Subsequently, in S21c, the processing device 9 detects the peak frequency fp (third peak frequency fp3) in the frequency spectrum obtained by the processing of S19c. Since the process of S21c is the same as the process of S21 described in the first embodiment (see FIG. 9), detailed description thereof will be omitted.

Subsequently, in S54, the processing device 9 calculates the combined peak frequency fp. The processing device 9 calculates the combined peak frequency fp based on the first peak frequency fp1 detected in S21a, the second peak frequency fp2 detected in S21b, and the third peak frequency fp3 detected in S21c. The processing device 9 can calculate the combined peak frequency fp by the following equation (2). The calculation method of the combined peak frequency fp is not particularly limited.

Subsequently, in S23, the processing device 9 specifies the blood flow velocity based on the synthetic peak frequency fp calculated in S54. Since the process of S23 has been described in the first embodiment, detailed description thereof will be omitted (see FIG. 9). Further, since the processing after S23 has also been described in the first embodiment, detailed description thereof will be omitted (see FIG. 9).

The measuring device 1 according to the third embodiment has been described above. As is clear from the above description, the measuring device 1 according to the third embodiment includes a first blocking device 5a that blocks the first laser beam L1 and a second blocking device 5b that blocks the second laser beam L2. I have. The processing device 9 includes a signal output by the light receiving device 3 when both the first blocking device 5a and the second blocking device 5b are in the non-blocking state, and a second blocking device while the first blocking device 5a is in the blocking state. A signal output by the light receiving device 3 when the 5b is in the non-blocking state and a signal output by the light receiving device 3 when the first blocking device 5a is in the non-blocking state while the second blocking device 5b is in the blocking state. And, the flow velocity of the blood hitting the intersection 10 is specified based on (S51-S23).

According to this configuration, the blood flow velocity is accurate by specifying the blood flow velocity by combining the blocked state / non-blocked state of the first blocking device 5a and the blocked / non-blocking state of the second blocking device 5b. Can be well identified.

Although specific examples of the present invention have been described in detail above, these are merely examples and do not limit the scope of claims. The techniques described in the claims include various modifications and modifications of the specific examples illustrated above. The technical elements described herein or in the drawings exhibit their technical usefulness alone or in various combinations, and are not limited to the combinations described in the claims at the time of filing. In addition, the techniques illustrated in the present specification or drawings can achieve a plurality of purposes at the same time, and achieving one of the purposes itself has technical usefulness.

1: Measuring device 2: Irradiating device 3: Light receiving device 4: Display device 5: Breaking device 5a: First blocking device 5b: Second blocking device 8: Housing 9: Processing device 10: Intersection 21: Light emitting element 22: Collimator Meter lens 23: Diffraction grating 25: Moving device 31: Light receiving element 35: Light passing hole 36: Incident port 37: Exit port 43: First mirror 44: Second mirror 51: Frame member 52: Opening / closing member 53: Opening 81 : Tip member 82: Opening 85: Protrusion 241: First reflecting surface 242: Second reflecting surface 243: First non-reflecting surface 251: Bolt 252: Linear encoder

Claims (5)

An irradiation device that irradiates the body with the first laser beam and the second laser beam that intersects the first laser beam.
A light receiving device that receives scattered light generated by the intersection of the first laser light and the second laser light irradiated by the irradiating device hitting blood flowing in the body and outputs a signal corresponding to the received scattered light.
Display device and
Equipped with a processing device,
The processing device is a measuring device that identifies the flow velocity of blood hitting the intersection based on a signal output by the light receiving device and displays the specified blood flow velocity on the display device. The measuring device according to claim 1, wherein the processing device displays a display representing an artery or a vein on the display device when the flow rate of the specified blood is faster than a predetermined first flow rate. It further includes a first blocking device that blocks the first laser light irradiated by the irradiation device.
The measuring device according to claim 1 or 2, wherein the first blocking device is configured to be able to switch between a blocking state that blocks the first laser light and a non-blocking state that does not block the first laser light. Further, a second blocking device for blocking the second laser light irradiated by the irradiation device is provided.
The second blocking device is configured to be able to switch between a blocking state that blocks the second laser beam and a non-blocking state that does not block the second laser light.
The processing device includes a signal output by the light receiving device when both the first blocking device and the second blocking device are in the non-blocking state, and the second blocking device while the first blocking device is in the blocking state. A signal output by the light receiving device when the device is in the non-blocking state and a signal output by the light receiving device when the first blocking device is in the non-blocking state while the second blocking device is in the blocking state. The measuring device according to claim 3, wherein the flow velocity of blood hitting the intersection is specified based on the above. The processing device is based on a signal output by the light receiving device when the first blocking device is in the non-blocking state and a signal output by the light receiving device when the first blocking device is in the blocking state. The measuring device according to claim 3, wherein the flow velocity of blood hitting the intersection is specified.

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