JPWO2020175515A1 - Blood vessel position detection device and blood flow measurement device - Google Patents

Abstract

The blood flow rate measuring device (10) includes a plurality of transducers (41, 42, 43), a calculation unit (32), and a notification unit (60). Each of the plurality of transducers (41, 42, 43) has a wavefront that transmits an ultrasonic wave to an object to be inspected and receives an echo of the ultrasonic wave. The wavefronts of the plurality of transducers (41, 42, 43) are aligned along the first direction of the inspection housing mounted on the inspection object. The calculation unit (32) detects the position of the blood vessel (90) in the examination target in the first direction from the difference in the time characteristics of the echo amplitudes of the plurality of transducers (41, 42, 43), and corrects the position. Generate information. The notification unit (60) gives a notification according to the position correction information.

Description

The present invention relates to a blood vessel position detecting device for detecting the position of a blood vessel to be measured for blood flow rate, and a blood flow rate measuring device.

Patent Document 1 describes a probe for examining a carotid artery. The probe described in Patent Document 1 includes a plurality of transducers. The plurality of transducers are arranged in two dimensions.

When examining the carotid artery, for example, the technician places a probe on the patient's neck to image the carotid artery. As a result, an echo image of the carotid artery is acquired.

Special Table 2016-525405

However, in the configuration described in Patent Document 1, it is not easy to arrange the probe at a position suitable for inspection. The position suitable for the test is, for example, a position where the transducer for the test can more accurately measure the blood flow rate of the blood vessel to be measured.

Therefore, an object of the present invention is to provide a blood vessel position detecting device capable of easily arranging a transducer for inspection at an optimum position for inspection, and a blood flow rate measuring device using this blood vessel position detecting device. be.

The blood vessel position detecting device of the present invention includes a plurality of transducers, a calculation unit, and a housing for inspection. Each of the plurality of transducers has a wavefront that transmits ultrasonic waves to an object to be inspected and receives an echo of the ultrasonic waves, and is arranged in a first direction substantially parallel to the wavefront. The calculation unit detects the position of the blood vessel in the examination target in the first direction from the difference in the temporal characteristics of the echo amplitudes of the plurality of transducers, and generates the position correction information. In the inspection housing, a plurality of transducers are arranged in the first direction and attached to the inspection target body.

In this configuration, the correction information of the position of the blood vessel can be known. Therefore, the subject to be inspected (the subject to be inspected), the companion, or the medical staff (nurse, technician, doctor, paramedic, etc.) determines the relationship between the position of the transducer for inspection and the position of the blood vessel. Easy to grasp.

According to the present invention, it becomes easy to place the transducer for inspection in the optimum position for inspection.

FIG. 1 is a functional block diagram of the blood flow rate measuring device. FIG. 2A is a schematic external view of the blood flow rate measuring device, and FIG. 2B is a perspective view showing a state in which the blood flow measuring device is attached. 3A is a diagram showing the front surface of the measurement patch, FIG. 3B is a diagram showing the side surface of the measurement patch, and FIG. 3C is a diagram showing the back surface of the measurement patch. It is a figure. FIG. 4A is a diagram showing an example of the positional relationship between the blood vessel and each transducer, and FIG. 4B is an example of the time characteristic of the amplitude of each echo signal in the positional relationship of FIG. 4A. It is a graph which shows. FIG. 5A is a diagram showing an example of the positional relationship between the blood vessel and each transducer, and FIG. 5B is an example of the time characteristic of the amplitude of each echo signal in the positional relationship of FIG. 5A. It is a graph which shows. FIG. 6A is a diagram showing an example of the positional relationship between the blood vessel and each transducer, and FIG. 6B is an example of the time characteristic of the amplitude of each echo signal in the positional relationship of FIG. 6A. It is a graph which shows. FIG. 7 is a diagram showing the concept of alignment in the extending direction of the blood vessel. FIG. 8 is a diagram for explaining the concept of measuring blood flow rate. FIG. 9 is a diagram showing an arrangement mode of a plurality of transducers in the measurement patch. FIG. 10 (A) is a diagram showing a state in which a plurality of transducers are arranged on the person to be inspected, and FIG. 10 (B) shows a driving state when a first ultrasonic wave is transmitted, and FIG. 10 (C) is shown. ) Shows the driving state when transmitting the second ultrasonic wave, and FIG. 10D shows the driving state when transmitting the third ultrasonic wave. 11 (A) is a diagram showing an example of the positional relationship between the blood vessel and each transducer, and FIG. 11 (B) is an example of the time characteristic of the amplitude of each echo signal in the positional relationship of FIG. 11 (A). It is a graph which shows. FIG. 12A is a diagram showing an example of the positional relationship between the blood vessel and each transducer, and FIG. 12B is an example of the time characteristic of the amplitude of each echo signal in the positional relationship of FIG. 12A. It is a graph which shows. 13 (A), 13 (B), and 13 (C) are diagrams showing other configuration examples of the measurement patch. FIG. 14 is a diagram showing another configuration example of the measurement patch. FIG. 15A is a diagram showing another configuration example of the measurement patch, and FIGS. 15B and 15C are diagrams showing the arrangement state of the measurement patch with respect to the blood vessel. FIG. 16 is a functional block diagram of the blood flow rate measuring device. FIG. 17 is a functional block diagram of the blood flow rate measuring device. FIG. 18A is a diagram showing another configuration example of the notification unit, and FIGS. 18B, 18C, and 18D are diagrams showing a notification example in the notification unit. FIG. 18E is a diagram showing a configuration example further derived from the notification unit. FIG. 19 is a perspective view showing another wearing state of the blood flow measuring device.

(First Embodiment)
The blood vessel position detecting device and the blood flow rate measuring device according to the first embodiment of the present invention will be described with reference to the drawings. FIG. 1 is a functional block diagram of the blood flow rate measuring device. FIG. 2A is a schematic external view of the blood flow rate measuring device, and FIG. 2B is a perspective view showing a state in which the blood flow measuring device is attached. 3A is a diagram showing the front surface of the measurement patch, FIG. 3B is a diagram showing the side surface of the measurement patch, and FIG. 3C is a diagram showing the back surface of the measurement patch. It is a figure. In the following, the case where the test target for detecting a blood vessel and measuring the blood flow is a human (test subject) and the target blood vessel is the common carotid artery will be described as an example.

(About the functional block of the blood flow measuring device)
As shown in FIG. 1, the blood flow rate measuring device 10 includes a signal control unit 31, a calculation unit 32, a plurality of transducers, and a notification unit 60. The plurality of transducers include a transducer 41, a transducer 42, a transducer 43, a transducer 51, and a transducer 52. Further, the blood flow rate measuring device 10 includes a battery 300.

The signal control unit 31, the calculation unit 32, and the battery 300 are provided in the main body 30. The transducer 41, the transducer 42, the transducer 43, the transducer 51, the transducer 52, and the notification unit 60 are mounted on the measurement patch 20. The measurement patch 20 corresponds to the "housing for measurement" of the present invention. The transducer 41, the transducer 42, and the transducer 43 correspond to the "first transducer", the "second transducer", and the "third transducer" of the present invention, respectively. The transducer 51 and the transducer 52 correspond to the "first blood flow rate measuring transducer" and the "second blood flow rate measuring transducer" of the present invention, respectively. The transducer 51 and the transducer 52 are provided with a transmission unit and a reception unit, respectively, for measurement in the Doppler mode.

The signal control unit 31 and the calculation unit 32 are realized by an electronic circuit, an IC, or the like. The notification unit 60 is realized by an element capable of notifying the outside such as a light emitting element such as an LED, a speaker, and a vibration element.

The signal control unit 31 is connected to the transducer 41, the transducer 42, the transducer 43, the transducer 51, and the transducer 52. The signal control unit 31 is connected to the calculation unit 32.

The calculation unit 32 is connected to the notification unit 60.

The battery 300 is connected to the signal control unit 31 and the calculation unit 32, and supplies power to the signal control unit 31 and the calculation unit 32. Further, the battery 300 is connected to the notification unit 60 as needed to supply power to the notification unit 60. If power can be supplied from the outside, the battery 300 can be omitted. However, by using the battery 300, the blood flow rate measuring device 10 can be easily carried, and the restrictions on the places of use are relaxed.

The signal control unit 31 outputs a transmission control signal to the transducer 41, the transducer 42, the transducer 43, the transducer 51, and the transducer 52.

The signal control unit 31 performs transmission control for detecting the position of a blood vessel with respect to the transducer 41, the transducer 42, and the transducer 43. For example, the signal control unit 31 controls the transmission of ultrasonic waves so as to obtain an echo signal used in the A mode or the B mode.

Further, the signal control unit 31 performs transmission control for measuring the blood flow rate with respect to the transducer 51 and the transducer 52. For example, the signal control unit 31 controls the transmission of ultrasonic waves so as to obtain an echo signal used in the Doppler mode.

After the measurement patch 20 is placed at an appropriate position as described later, the echo signals from the transducer 41, the transducer 42, and the transducer 43 can also be used for diagnosis using the A mode or the B mode. It is possible.

The transducer 41, the transducer 42, the transducer 43, the transducer 51, and the transducer 52 receive a transmission control signal from the signal control unit 31 and excite them to transmit ultrasonic waves.

The transducer 41, the transducer 42, the transducer 43, the transducer 51, and the transducer 52 have directivity in a predetermined direction. The directivity in a predetermined direction is, for example, the directivity in which ultrasonic waves are transmitted in all directions from the transmission / reception wavefront, and as an example thereof, unidirectionality can be adopted. The transducer 41, the transducer 42, the transducer 43, the transducer 51, and the wave front of the transducer 52 face the inspection target side. Then, the ultrasonic waves transmitted from the transducer 41, the transducer 42, the transducer 43, the transducer 51, and the transducer 52 are reflected in the person to be inspected. For example, ultrasonic waves are reflected at discontinuous positions of acoustic impedance, such as the wall of the common carotid artery. The echo signal due to this reflection is received by the transducer 41, the transducer 42, the transducer 43, the transducer 51, and the transducer 52.

The transducer 41, the transducer 42, the transducer 43, the transducer 51, and the transducer 52 convert the echo signal into an electric signal and output it to the signal control unit 31.

The signal control unit 31 performs filter processing such as noise removal, amplification processing, and the like on the echo signal, and outputs the echo signal to the calculation unit 32.

The calculation unit 32 detects the position of the blood vessel by using the echo signal from the transducer 41, the echo signal of the transducer 42, and the echo signal of the transducer 43. The detection of the position of a blood vessel is performed by an echo signal in A mode or B mode. A specific method for detecting the position of a blood vessel will be described later. The calculation unit 32 generates correction information for the position of the measurement patch 20 by using the detection result of the position of the blood vessel. The position correction information is, for example, the movement direction of the measurement patch 20, the movement amount, the arrangement of the measurement patch 20 at the optimum position, and the like. The calculation unit 32 controls the notification mode of the notification unit 60 by using the position correction information.

The notification unit 60 gives a notification according to the notification mode. In other words, the notification unit 60 makes a notification based on the position correction information.

The calculation unit 32 measures the blood flow rate using the echo signal from the transducer 51 and the echo signal of the transducer 52. Blood flow measurement is performed using Doppler mode echo signals. A specific method for measuring blood flow will be described later. The calculation unit 32 stores the measured blood flow rate in a storage unit (not shown) or outputs the measured blood flow rate to an external device via an output terminal (not shown).

The blood flow rate measuring device 10 functions as a blood vessel position detecting device if the blood flow rate is not measured, that is, if only the position of the blood vessel is detected.

(About the structure of the blood flow measuring device)
The blood flow rate measuring device 10 includes a measuring patch 20 and a main body 30. The main body 30 is, for example, a U-shaped rod-shaped body as shown in FIG. 2 (A). As shown in FIG. 2B, the main body 30 is attached so as to be placed on the shoulder 991 so as to surround the neck 990 of the examinee 99, for example. Therefore, it is preferable that a cushioning member is arranged on the outer surface of the main body 30. As a result, it does not hurt even if the person to be inspected wears it, and the usability is improved.

The measurement patch 20 is connected to the main body 30 by the cable 21. The transmission line connecting the above-mentioned plurality of transducers and the signal control unit 31 is arranged in the cable 21. In addition, in FIG. 2A and FIG. 2B, the number of measurement patches 20 is two, but may be one. In the case of two, as shown in FIG. 2B, they are arranged so as to overlap the left and right common carotid arteries in the neck 990, and the detection of the position of the blood vessel and the measurement of the blood flow with respect to both the left and right common carotid arteries are performed. , Can be done at the same time.

The configuration of the blood flow rate measuring device 10 is not limited to this, and for example, the main body 30 and the measuring patch 20 may be integrated to eliminate the cable exposed to the outside. Further, after the main body 30 and the measurement patch 20 are integrated, the main body 30 is wrapped around the neck of the inspection target person, and the main body 30 gives a certain holding force to the neck of the inspection target person. It may be a thing or the like.

As shown in FIGS. 2A, 2B, 3A, 3B, and 3C, the measurement patch 20 includes a substantially rectangular parallelepiped housing 200. The housing 200 corresponds to the "housing for inspection" of the present invention. For example, the dimension of the housing 200 in the thickness direction (Z direction) is smaller than the dimension in the other two directions (X direction and Y direction). The dimensions of the housing 200 in the X and Y directions are, for example, about 20 mm to about 30 mm. This shape is possible because, as will be described later, the housing 200 includes only a plurality of transducers and a notification unit 60. As a result, the person to be inspected or the accompanying person in the examination (an attendant or a medical worker (nurse, technician, doctor, paramedic, etc.)) can easily handle the measurement patch 20. In addition, the discomfort of the inspection target person due to the use of the measurement patch 20 is reduced. Further, the measurement patch 20 may be provided with an adhesive layer such as gel on the back surface 202 side. By providing such an adhesive layer, the inspection subject can easily attach and detach the measurement patch 20, and can prevent the arrangement position of the measurement patch 20 from fluctuating during the inspection. Also, instead of providing an adhesive layer, the measurement patch 20 is simply attached to the subject to be inspected with medical tape, or fixed to the neck by wrapping it with a cloth-like member having a certain length such as a bandage or band. You may.

More specifically, the measurement patch 20 has the following structure. The housing 200 includes a front surface 201, a back surface 202, a side surface 203, a side surface 204, a side surface 205, and a side surface 206. The front surface 201 and the back surface 202 are planes orthogonal to the Z direction. The side surface 203 and the side surface 204 are separated along the X direction and are planes orthogonal to the X direction. The side surface 205 and the side surface 206 are separated along the Y direction and are planes orthogonal to the Y direction. The back surface 202 is a surface arranged so as to face the skin of the subject to be inspected, and corresponds to the “detection surface” of the present invention.

The back surface 202 has a transmission / reception surface of the transducer 41, a transmission / reception surface of the transducer 42, a transmission / reception surface of the transducer 43, a transmission / reception surface of the transducer 51, and a transmission / reception surface of the transducer 52. The transmission / reception surface of the transducer 41, the transmission / reception surface of the transducer 42, the transmission / reception surface of the transducer 43, the transmission / reception surface of the transducer 51, and the transmission / reception surface of the transducer 52 are arranged at positions substantially centered in the Y direction on the back surface 202. The transmission / reception surface of the transducer 41, the transmission / reception surface of the transducer 42, the transmission / reception surface of the transducer 43, the transmission / reception surface of the transducer 51, and the transmission / reception surface of the transducer 52 are along the X direction (corresponding to the first direction) on the back surface 202. , Are arranged in a straight line. The transmission / reception surface of the transducer 41, the transmission / reception surface of the transducer 42, the transmission / reception surface of the transducer 43, the transmission / reception surface of the transducer 51, and the transmission / reception surface of the transducer 52 may be exposed on the back surface 202, but they may be exposed from the transmission / reception surface. It is preferable that a matching layer of acoustic impedance, which will be described later, is arranged in the transmission direction of the sound wave.

At this time, the wave front of the transducer 51, the wave front of the transducer 41, the wave front of the transducer 42, the wave front of the transducer 43, and the wave front of the transducer 52 are arranged in this order from the side surface 203 to the side surface 204. There is.

The wavefront of the transducer 42 is arranged at the center of the back surface 202 in the X direction, that is, at the center of the back surface 202.

It is preferable that the distance between the center of the transmission / reception surface of the transducer 42 and the center of the transmission / reception surface of the transducer 41 and the distance between the center of the transmission / reception surface of the transducer 42 and the center of the transmission / reception surface of the transducer 43 are the same. These distances are set based on the average diameter of the common carotid artery. For example, these distances are shorter than the average diameter of the common carotid artery (about 6 mm to about 8 mm) and are set to predetermined values within the range accommodated in the housing 200.

The distance between the center of the transmission / reception surface of the transducer 51 and the center of the transmission / reception surface of the transducer 52 is preferably about twice the average value of the distance from the epidermis of the examinee to the common carotid artery.

The transmission / reception surface of the transducer 41, the transmission / reception surface of the transducer 42, and the transmission / reception surface of the transducer 43 are parallel to the back surface 202. The wavefront of the transducer 51 and the wavefront of the transducer 52 have a predetermined angle (eg, about 45 °) with respect to the back surface.

On the surface 201, a light emitting part of the light emitting element 611, a light emitting part of the light emitting element 6121, a light emitting part of the light emitting element 6122, a light emitting part of the light emitting element 6131, and a light emitting part of the light emitting element 6132 are arranged.

Further, a sound emitting portion 620 of the speaker is formed on the surface 201. The sound emitting unit 620 is, for example, a through hole formed at a position facing the sound emitting surface of the speaker (arranged in the housing 200) on the surface 201. The measurement patch 20 may be provided with at least one of a plurality of light emitting elements and a sound emitting unit 620.

The light emitting portion of the light emitting element 611 is arranged at the center of the surface 201 in the X direction and the Y direction. The light emitting part of the light emitting element 6121, the light emitting part of the light emitting element 6122, the light emitting part of the light emitting element 6131, and the light emitting part of the light emitting element 6132 are arranged in a straight line together with the light emitting part of the light emitting element 611 along the X direction. There is. At this time, from the side surface 203 to the side surface 204, the light emitting part of the light emitting element 6122, the light emitting part of the light emitting element 6121, the light emitting part of the light emitting element 611, the light emitting part of the light emitting element 6131, and the light emitting part of the light emitting element 6132 are in this order. It is arranged in.

As shown in FIG. 2A, the shape of the light emitting portion may be circular or rectangular.

These light emitting elements are controlled to emit light according to the above-mentioned position correction information. For example, when the measurement patch 20 is in the optimum position, the light emitting element 611 is turned on and the other light emitting elements are turned off. Further, for example, when the correction for moving the measurement patch 20 in the − direction in the X direction is required, the light emitting element 6121 and the light emitting element 6122 are turned on, and the other light emitting elements are turned off. Further, for example, when the correction for moving the measurement patch 20 in the + direction in the X direction is required, the light emitting element 6131 and the light emitting element 6132 are turned on, and the other light emitting elements are turned off. At this time, the emission intensity and the emission mode may be adjusted in each case according to the length required for movement.

(Method of detecting the position of blood vessels)
FIG. 4A is a diagram showing an example of the positional relationship between the blood vessel and each transducer, and FIG. 4B is an example of the time characteristic of the amplitude of each echo signal in the positional relationship of FIG. 4A. It is a graph which shows. 4 (A) and 4 (B) show a case where the measurement patch 20 is arranged at an optimum position with respect to the width direction of the blood vessel 90.

FIG. 5A is a diagram showing an example of the positional relationship between the blood vessel and each transducer, and FIG. 5B is an example of the time characteristic of the amplitude of each echo signal in the positional relationship of FIG. 5A. It is a graph which shows. 5 (A) and 5 (B) show a case where the measurement patch 20 is arranged so as to be displaced in the −X direction with respect to the width direction of the blood vessel 90.

FIG. 6A is a diagram showing an example of the positional relationship between the blood vessel and each transducer, and FIG. 6B is an example of the time characteristic of the amplitude of each echo signal in the positional relationship of FIG. 6A. It is a graph which shows. 6 (A) and 6 (B) show a case where the measurement patch 20 is arranged so as to be offset in the + X direction with respect to the width direction of the blood vessel 90.

When detecting the position of a blood vessel, as shown in FIGS. 4 (A), 5 (A), and 6 (A), the X direction of the measurement patch 20 in which the transducer 41, the transducer 42, and the transducer 43 are arranged is the blood vessel. The measurement patch 20 is placed on the skin surface 901 of the subject to be inspected so as to be substantially parallel to the width direction of the 90. At this time, it is preferable to dispose the matching layer 400 of acoustic impedance between the transducer 41, the transducer 42, and the transducer 43 and the skin surface 901.

Here, the matching layer 400 of the acoustic impedance is set to take a value between the acoustic impedance of the human body (the person to be inspected) and the acoustic impedance of the transducer. By doing so, it is possible to suppress the reflection of the ultrasonic waves generated by each transducer on the skin surface, and it is possible to improve the sensitivity. Further, the matching layer 400 of acoustic impedance is not limited to a single layer, and may be provided with a plurality of layers. The acoustic impedance matching layer 400 is made of a known resin material or the like, but may also serve as an adhesive material (gel or the like) for adhering the measurement patch 20 to the human body.

The placement position of the measurement patch is easily determined according to the blood vessel 90. For example, if the blood vessel 90 is a common carotid artery, the extending direction of the blood vessel 90 is a direction orthogonal to the circumferential direction of the neck. Therefore, if the blood vessel 90 is the common carotid artery, the measurement patch 20 may be arranged so that the X direction is parallel to the circumferential direction of the neck.

The calculation unit 32 detects the reception time (peak time) by detecting the peak of the amplitude of the echo signal received by each transducer.

(When the measurement patch 20 is placed at the optimum position with respect to the width direction of the blood vessel 90)
As shown in FIG. 4A, when the measurement patch 20 is arranged at an optimum position with respect to the width direction of the blood vessel 90, the distance D42 between the transmission / reception surface of the transducer 42 and the blood vessel 90 is the transducer 41. It is shorter than the distance D41 between the transmission / reception surface and the blood vessel 90 and the distance D43 between the transmission / reception surface of the transducer 43 and the blood vessel 90. Further, the distance D41 between the wave front of the transducer 41 and the blood vessel 90 and the distance D43 between the wave front of the transducer 43 and the blood vessel 90 are substantially the same. That is, D42 <D41≈D43.

Therefore, when the transducer 41, the transducer 42, and the transducer 43 transmit ultrasonic waves, the echo signal of the transducer 42 is received earliest, and then, at about the same time, the echo signal of the transducer 41 and the echo signal of the transducer 43 are received. ..

Therefore, as shown in FIG. 4B, the time difference Δt42 between the echo signal reception time t42 of the transducer 42 and the ultrasonic transmission time t0 is the echo signal reception time t41 of the transducer 41 and the ultrasonic transmission. It is shorter than the time difference Δt41 from the time t0. Similarly, the time difference Δt42 between the echo signal reception time t42 of the transducer 42 and the ultrasonic transmission time t0 is shorter than the time difference Δt43 between the echo signal reception time t43 of the transducer 43 and the ultrasonic transmission time t0. .. The time difference Δt41 and the time difference Δt43 are substantially the same.

As a result, if the time difference Δ42 is smaller than the time difference Δt41 and the time difference Δt43, the calculation unit 32 determines that the measurement patch 20 is arranged at the optimum position in the width direction of the blood vessel 90. .. As described above, according to the present embodiment, the blood flow rate measuring device 10 can more accurately determine that the measuring patch 20 is arranged at the optimum position with respect to the width direction of the blood vessel 90.

Then, the notification unit 60 causes, for example, the light emitting element 611 to emit light according to this result. Thereby, the test subject and the test companion (attendant or medical worker) can easily determine that the measurement patch 20 is arranged at the optimum position with respect to the width direction of the blood vessel 90. ..

The calculation unit 32 can also determine that the measurement patch 20 is arranged at an optimum position in the width direction of the blood vessel 90 by using the reception time. However, by using the time difference, even if the transmission time of each transducer is different, the calculation unit 32 indicates that the measurement patch 20 is arranged at the optimum position in the width direction of the blood vessel 90. It can be judged accurately.

(When the measurement patch 20 is not placed in the optimum position with respect to the width direction of the blood vessel 90)
(In the first case)
As shown in FIG. 5A, when the measurement patch 20 is arranged with the blood vessel 90 displaced from the transducer 41 side in the width direction of the blood vessel 90, the transmission / reception surface of the transducer 41 and the blood vessel 90 The distance D41 from and to is shorter than the distance D42 between the wave transmission / reception surface of the transducer 42 and the blood vessel 90. Further, the distance D42 between the wave front of the transducer 42 and the blood vessel 90 is shorter than the distance D43 between the wave front of the transducer 43 and the blood vessel 90. That is, D41 <D42 <D43.

Therefore, when the transducer 41, the transducer 42, and the transducer 43 transmit ultrasonic waves, the echo signal of the transducer 41 is received, then the echo signal of the transducer 42 is received, and further, the echo signal of the transducer 43 is received. ..

Therefore, as shown in FIG. 5B, the time difference Δt41 between the echo signal reception time t41 of the transducer 41 and the ultrasonic transmission time t0 is the echo signal reception time t42 of the transducer 42 and the ultrasonic transmission. It is shorter than the time difference Δt42 from the time t0. The time difference Δt42 between the echo signal reception time t42 of the transducer 42 and the ultrasonic transmission time t0 is shorter than the time difference Δt43 between the echo signal reception time t43 of the transducer 43 and the ultrasonic transmission time t0.

As a result, if the time difference Δ41 is smaller than the time difference Δt42 and the time difference Δt43, the calculation unit 32 states that the measurement patch 20 is displaced from the transducer 41 side in the width direction of the blood vessel 90. judge. That is, it is determined that the measurement patch 20 is displaced in the −X direction with respect to the width direction of the blood vessel 90. As described above, according to the present embodiment, the blood flow rate measuring device 10 can more accurately determine that the measurement patch 20 is displaced from the optimum position in the width direction of the blood vessel 90. ..

Then, according to this result, the notification unit 60 causes the light emitting element 611 to emit light, for example, the light emitting element 6131 and the light emitting element 6132 in the + X direction. As a result, the test subject and the test companion (attendant or medical staff) can be placed in the optimum position by shifting the measurement patch 20 in the + X direction with respect to the width direction of the blood vessel 90. It is easy to judge.

(In the second case)
As shown in FIG. 6A, when the measurement patch 20 is arranged with the blood vessel 90 displaced from the transducer 43 side in the width direction of the blood vessel 90, the transmission / reception surface of the transducer 43 and the blood vessel 90 The distance D43 from and to is shorter than the distance D42 between the wave transmission / reception surface of the transducer 42 and the blood vessel 90. Further, the distance D42 between the wave front of the transducer 42 and the blood vessel 90 is shorter than the distance D41 between the wave front of the transducer 41 and the blood vessel 90. That is, D43 <D42 <D41.

Therefore, when the transducer 41, the transducer 42, and the transducer 43 transmit ultrasonic waves, the echo signal of the transducer 43 is received, then the echo signal of the transducer 42 is received, and further, the echo signal of the transducer 41 is received. ..

Therefore, as shown in FIG. 6B, the time difference Δt43 between the echo signal reception time t43 of the transducer 43 and the ultrasonic transmission time t0 is the echo signal reception time t42 of the transducer 42 and the ultrasonic transmission. It is shorter than the time difference Δt42 from the time t0. The time difference Δt42 between the echo signal reception time t42 of the transducer 42 and the ultrasonic transmission time t0 is shorter than the time difference Δt41 between the echo signal reception time t41 of the transducer 41 and the ultrasonic transmission time t0.

As a result, if the time difference Δ43 is smaller than the time difference Δt42 and the time difference Δt41, the calculation unit 32 states that the measurement patch 20 is displaced from the transducer 43 side in the width direction of the blood vessel 90. judge. That is, it is determined that the measurement patch 20 is displaced in the + X direction with respect to the width direction of the blood vessel 90. As described above, according to the present embodiment, the blood flow rate measuring device 10 can more accurately determine that the measurement patch 20 is displaced from the optimum position in the width direction of the blood vessel 90. .. Further, as shown in FIG. 6A, even if the blood vessel 90 and the measurement patch 20 do not overlap each other in a plan view, the positional deviation between the blood vessel 90 and the measurement patch 20 can be accurately determined.

Then, according to this result, the notification unit 60 causes the light emitting element 611 to emit light, for example, the light emitting element 6121 and the light emitting element 6122 in the −X direction. As a result, the test subject and the test companion (attendant or medical staff) can be placed in the optimum position by shifting the measurement patch 20 in the −X direction with respect to the width direction of the blood vessel 90. , Easy to judge.

Further, when the amount of deviation is large as shown in FIG. 6A, for example, the notification unit 60 increases the brightness of the light emitting element 6121 and the light emitting element 6122. As a result, the test subject and the test companion (attendant or medical staff) can be placed in the optimum position by greatly shifting the measurement patch 20 in the −X direction with respect to the width direction of the blood vessel 90. Can be easily determined. For example, the notification unit 60 may change the colors of the light emitting element 6121 and the light emitting element 6122 instead of increasing the brightness of the light emitting element 6121 and the light emitting element 6122. That is, when the amount of deviation is small, the color may change to blue, and when the amount of deviation is large, the color may change to red or the like so that the person to be inspected and the companion of the inspection recognize the amount of deviation.

The calculation unit 32 can also determine that the measurement patch 20 is displaced from the optimum position in the width direction of the blood vessel 90 by using the reception time. However, by using the time difference, even if the transmission time of each transducer is different, the calculation unit 32 is arranged so that the measurement patch 20 is displaced from the optimum position in the width direction of the blood vessel 90. Can be accurately determined.

With the above configuration, the measurement patch 20 is easily arranged so that the blood vessel 90 and the transducer 42 overlap each other in the width direction of the blood vessel 90. In this state, the measuring patch 20 is typically 90 so that the transducer 41, the transducer 42, the transducer 43, the transducer 51, and the transducer 52 are aligned in the length direction (Y direction) of the blood vessel in a plan view. ° Can be rotated. The rotation can be, for example, manual or automatic. In the case of automatic, for example, a rotation jig may be arranged between the back surface 202 and the skin surface 901 on the back surface 202 side of the measurement patch 20, and the measurement patch 20 may be provided with a rotation drive mechanism. .. With this rotation jig, the measurement patch 20 is rotated by, for example, 90 °. By rotating the measuring patch 20 by, for example, 90 °, the transducer 41, the transducer 42, the transducer 43, the transducer 51, and the transducer 52 are arranged along the extending direction of the blood vessel 90, and are arranged in the blood vessel 90 in a plan view. Overlap. Even in this state, the blood flow rate can be measured. However, by arranging the measurement patch 20 at an optimum position for measuring the blood flow rate in the direction extending the blood vessel 90, the measurement of the blood flow rate becomes more accurate. Next, a method of aligning the positions will be described.

(Method of arranging at a specific position in the extending direction of the blood vessel 90)
FIG. 7 is a diagram showing the concept of alignment in the extending direction of the blood vessel. As shown in FIG. 7, when the measurement patch 20 is arranged at a specific position in the extending direction of the blood vessel 90, the X direction and the extending direction of the blood vessel 90 of the measurement patch 20 are parallel to each other. The above-mentioned alignment in the width direction causes the transducer 41, the transducer 42, and the transducer 43 to overlap with different positions in the extending direction of the blood vessel 90.

Here, the blood vessel 90 is branched and connected to the blood vessel 91 and the blood vessel 92. For example, when the blood vessel 90 is the common carotid artery, the blood vessel 91 is the external carotid artery and the blood vessel 92 is the internal carotid artery. By utilizing this feature, the measurement patch 20 can be placed at a specific position in the extending direction of the blood vessel 90.

Generally, in the case of the common carotid artery, the optimum point PD for measuring blood flow is a predetermined distance from the bifurcation point PJ between the common carotid artery to the external carotid artery and the internal carotid artery to the common carotid artery side (for example,). It is located at a distance of about 1 cm from the branch point PJ). Therefore, the distance between the optimum point PD and the branch point PJ is set to be the same as the distance between the center of the wavefront of the transducer 42 and the center of the wavefront of the transducer 43.

Here, the external carotid artery (blood vessel 91) and the internal carotid artery (blood vessel 92) exist on the opposite side of the common carotid artery with respect to the bifurcation point PJ. Therefore, when the echo of the two blood vessels is obtained by the ultrasonic wave of the transducer 43, it can be determined that the center of the wavefront of the transducer 42 is arranged at the branch point PJ rather than the optimum point PD. Then, if the position of switching from the state where the echo of two blood vessels is obtained by the ultrasonic wave of the transducer 43 to the state where the echo of one blood vessel is obtained in the extending direction of the blood vessel is detected, the center of the wave front of the transducer 42 is detected. Overlaps the optimal point PD. As a result, the measurement patch 20 is arranged at a position suitable for measuring blood flow.

From this detection result, the calculation unit 32 can determine that the measurement patch 20 is arranged at a position suitable for measuring the blood flow rate even in the extending direction of the blood vessel 90.

Further, for example, in the calculation unit 32, when all the reception times are substantially the same or all the time differences are substantially the same, the measurement patch 20 is displaced more toward the blood vessel 90 with respect to the suitable position. It can be determined that there is. In this case, the notification unit 60 emits light so as to move the measurement patch 20 in the + X direction. As a result, even in the extending direction of the blood vessel 90, the person to be inspected and the accompanying person (an attendant or a medical worker) can easily arrange the measurement patch 20 in a suitable position by shifting the measurement patch 20 in the + X direction. Can be judged.

In the above description, the case of notifying by light emission is shown, but as described above, if the sound emitting unit 620 is provided, the blood flow rate measuring device 10 can perform the notification by sound. For example, it is possible to send guidance such as "Please move 1 cm upward". Thereby, for example, the person to be inspected can move the measurement patch 20 to a suitable position even if the light emitting state cannot be seen.

(Measurement method of blood flow rate)
FIG. 8 is a diagram for explaining the concept of measuring blood flow rate.

As described above, when the measurement patch 20 is arranged with respect to the optimum point PD of the blood vessel 90, the signal control unit 31 drives the transducer 51 and the transducer 52 in the Doppler mode. Then, the signal control unit 31 outputs the echo signal to the calculation unit 32. The calculation unit 32 calculates a Doppler component (measurement data) from the continuously obtained echo signal, and measures the blood flow rate from the Doppler component. The drive start trigger can be realized, for example, by outputting the detection result of the arrangement at the optimum point PD from the calculation unit 32 to the signal control unit 31.

Here, as described above, the transmission / reception surface of the transducer 51 and the transmission / reception surface of the transducer 52 are not parallel to the back surface 202 of the measurement patch 20. More specifically, as shown in FIG. 8, the transmission / reception surface of the transducer 51 is inclined so that the surface parallel to the back surface 202 and the direction orthogonal to the transmission / reception surface form an angle θ51. Further, the wave front of the transducer 52 is inclined so that the plane parallel to the back surface 202 and the direction orthogonal to the wave front of the transducer 52 form an angle θ52.

Further, the transmission / reception surface of the transducer 51 and the transmission / reception surface of the transducer 52 are inclined toward the arrangement region side of the transducer 41, the transducer 42, and the transducer 43, that is, the center side in the X direction of the measurement patch 20.

The total angle between the angle θ51 and the angle θ52 is approximately 90 °. In particular, it is better that the angle θ51 and the angle θ52 are both approximately 45 °.

Further, the distance between the center of the wave front of the transducer 51 and the center of the wave front of the transducer 52 is set to be about twice the distance between the skin surface 901 and the optimum point PD of the blood vessel 90. The distance between the skin surface 901 and the optimum point PD of the blood vessel 90 varies slightly from person to person, but is almost unchanged. Therefore, the distance between the center of the wavefront of the transducer 51 and the center of the wavefront of the transducer 52 can be uniquely set.

With such a configuration, the blood flow rate can be easily measured by using the sum of squares of the Doppler component of the echo signal of the transducer 51 and the Doppler component of the echo signal of the transducer 52.

Here, the optimum point PD is taken as an example, but if another measurement target point in the blood vessel 90 is determined, this measurement target point is replaced with the above-mentioned optimum point PD, and the transducer 51 and the transducer 52 are used. The arrangement mode may be adjusted.

(Second Embodiment)
The blood flow rate measuring device according to the second embodiment will be described with reference to the drawings. FIG. 9 is a diagram showing an arrangement mode of a plurality of transducers in the measurement patch.

The functional configuration of the blood flow measuring device according to the second embodiment is the same, and in the arrangement mode of the plurality of transducers of the measurement patch 20A, the ultrasonic wave mode, and the concept of detecting the position of the blood vessel, the first. It is different from the blood flow measuring device 10 according to the embodiment of. The same parts as the blood flow rate measuring device 10 in the blood flow rate measuring device according to the second embodiment will not be described.

The measurement patch 20A includes 11 transducers 401-411, a transducer 51, and a transducer 52. These are arranged in a straight line along the X direction. The 11 transducers 401-411 have a transducer 401, a transducer 402, a transducer 403, a transducer 404, a transducer 405, a transducer 406, a transducer 407, a transducer 408, a transducer 409, a transducer 410, and a transducer 411 from the side surface 203 to the side surface 204. They are arranged in the order of. The transducer 51 and the transducer 52 are arranged so as to sandwich the 11 transducers 401-411. The placement interval of the 11 transducers 401-411 is shorter than the placement interval of the transducers 401-403 shown in the first embodiment described above. The number of transducers is not limited to 11, and can be set as appropriate.

FIG. 10 (A) is a diagram showing a state in which a plurality of transducers are arranged on the person to be inspected, and FIG. 10 (B) shows a driving state when a first ultrasonic wave is transmitted, and FIG. 10 (C) is shown. ) Shows the driving state when transmitting the second ultrasonic wave, and FIG. 10D shows the driving state when transmitting the third ultrasonic wave. It should be noted that it is an example of these driving states, and the number of transducers to be driven at the time of transmitting each ultrasonic wave can be appropriately set according to the shape of the directivity of the ultrasonic wave. These ultrasonic waves correspond to the "super-directional ultrasonic waves" of the present invention.

As shown in FIG. 10B, by driving the transducers 401-407 and not the transducers 408-411, the ultrasonic wave S1 is, for example, a super-directional supersonic wave having a strong directivity directly under the transducer 404. It becomes a sound wave. Further, as shown in FIG. 10C, by driving the transducers 403-409 and not driving the transducers 401, 402, 410, 411, the ultrasonic wave S2 has a strong directivity directly under the transducer 406, for example. It becomes a super-directional ultrasonic wave that has. Further, as shown in FIG. 10 (D), by driving the transducer 405-411 and not driving the transducer 401-404, the ultrasonic wave S3 has, for example, super directivity having a strong directivity directly under the transducer 408. It becomes an ultrasonic wave of.

By switching the transducer to be driven in this way, the measurement patch 20 is super-directional with strong directivity in the direction orthogonal to the transmission / reception plane, and a plurality of super-directivity axes having different directivity axes in the X direction. Can transmit sound waves. By performing this control, the distance between the ultrasonic waves S1, the ultrasonic waves S2, and the ultrasonic waves S3 is larger than the distance between the transducer 41, the transducer 42, and the transducer 43 shown in the first embodiment described above. Can be shortened.

(Method of detecting the position of blood vessels)
11 (A) is a diagram showing an example of the positional relationship between the blood vessel and each transducer, and FIG. 11 (B) is an example of the time characteristic of the amplitude of each echo signal in the positional relationship of FIG. 11 (A). It is a graph which shows. 11 (A) and 11 (B) show a case where the measurement patch 20A is arranged at an optimum position with respect to the width direction of the blood vessel 90.

FIG. 12A is a diagram showing an example of the positional relationship between the blood vessel and each transducer, and FIG. 12B is an example of the time characteristic of the amplitude of each echo signal in the positional relationship of FIG. 12A. It is a graph which shows. 12 (A) and 12 (B) show a case where the measurement patch 20A is arranged so as to be displaced in the −X direction with respect to the width direction of the blood vessel 90.

When detecting the position of the blood vessel 90, as shown in FIGS. 11 (A) and 12 (A), the X direction of the measurement patch 20A in which a plurality of transducers 401-411 are lined up is substantially parallel to the width direction of the blood vessel 90. As such, the measurement patch 20 is placed on the skin surface 901 of the subject to be inspected.

The ultrasonic waves S1, the ultrasonic waves S2, and the ultrasonic waves S3 are super-directional. Therefore, the amplitude of the echo signal of the ultrasonic wave S1, the amplitude of the echo signal of the ultrasonic wave S2, and the amplitude of the echo signal of the ultrasonic wave S3 are echoes from the portion where the axis of directivity and the wall of the blood vessel 90 intersect. It depends largely on the signal strength. By utilizing this, the position of the blood vessel 90 can be detected as follows.

Time t411 is the time when the ultrasonic wave S1 hits the wall on the skin surface 901 side of the blood vessel 90 and the echo signal is received, and time t412 is the time when the ultrasonic wave S1 hits the wall on the skin surface 901 side of the blood vessel 90 and echoes. The time when the signal is received. The time difference ΔtS1 is the time difference between the time t411 and the time t412.

The time t421 is the time when the ultrasonic wave S2 hits the wall on the skin surface 901 side of the blood vessel 90 and the echo signal is received, and the time t422 is the time when the ultrasonic wave S2 hits the wall on the skin surface 901 side of the blood vessel 90 and echoes. The time when the signal is received. The time difference ΔtS2 is the time difference between the time t421 and the time t422.

Time t431 is the time when the ultrasonic wave S3 hits the wall on the skin surface 901 side of the blood vessel 90 and the echo signal is received, and time t432 is the time when the ultrasonic wave S2 hits the wall on the skin surface 901 side of the blood vessel 90 and echoes. The time when the signal is received. The time difference ΔtS3 is the time difference between the time t431 and the time t432.

(When the measurement patch 20 is placed at the optimum position with respect to the width direction of the blood vessel 90)
As shown in FIG. 11A, when the measurement patch 20A is arranged at an optimum position with respect to the width direction of the blood vessel 90, the time difference ΔtS2 is larger than the time difference ΔtS1 and the time difference ΔtS3. The time difference ΔtS1 and the time difference ΔtS3 are substantially the same.

As a result, if the time difference ΔtS2 is larger than the time difference ΔtS1 and the time difference ΔtS3, and the time difference ΔtS1 and the time difference ΔtS3 are substantially the same, the calculation unit 32 performs a measurement patch in the width direction of the blood vessel 90. It is determined that 20 is arranged at the optimum position. As described above, according to the present embodiment, the blood flow rate measuring device can more accurately determine that the measurement patch 20A is arranged at the optimum position in the width direction of the blood vessel 90.

Then, the notification unit 60 causes, for example, the light emitting element 611 to emit light according to this result. Thereby, the test subject and the test companion (attendant or medical worker) can easily determine that the measurement patch 20A is arranged at the optimum position with respect to the width direction of the blood vessel 90. ..

(When the measurement patch 20A is not placed in the optimum position with respect to the width direction of the blood vessel 90)
As shown in FIG. 12A, when the measurement patch 20A is deviated toward the transducer 51 (shifted in the −X direction) with respect to the width direction of the blood vessel 90, the time difference ΔtS1 is the time difference ΔtS2. Greater than. Further, in the case of FIG. 12A, since the ultrasonic wave S3 does not hit the blood vessel 90, the time difference with respect to the ultrasonic wave S3 is not detected. In this case, the time difference ΔtS3 can be regarded as 0.

As a result, if the time difference ΔtS1 is larger than the time difference ΔtS2 and the time difference ΔtS3, the calculation unit 32 determines that the measurement patch 20 is displaced in the −X direction with respect to the width direction of the blood vessel 90.

As described above, according to the present embodiment, the blood flow rate measuring device can more accurately determine that the measurement patch 20A is displaced from the optimum position in the width direction of the blood vessel 90.

Then, according to this result, the notification unit 60 causes the light emitting element 611 to emit light, for example, the light emitting element 6131 and the light emitting element 6132 in the + X direction. As a result, the test subject and the test companion (attendant or medical staff) can be placed in the optimum position by shifting the measurement patch 20 in the + X direction with respect to the width direction of the blood vessel 90. It is easy to judge.

Moreover, in such a configuration, the resolution of position detection is improved. As a result, the blood flow measuring device can detect the position of the blood vessel 90 with higher accuracy. In this embodiment, an embodiment in which three ultrasonic waves are transmitted is shown. However, the number of ultrasonic waves to be transmitted is not limited to three. For example, the blood flow measuring device may transmit more ultrasonic waves with shorter intervals between the ultrasonic waves. As a result, the detection of the blood vessel 90 becomes more accurate.

(Other configuration examples of measurement patches)
13 (A), 13 (B), 13 (C), and 14 are diagrams showing other configuration examples of the measurement patch. In the following, only the parts that are different from each of the above-mentioned measurement patch 20 and the measurement patch 20A will be described, and the description of the same parts will be omitted.

(Structure example of the first derivation)
As shown in FIG. 13A, the measurement patch 20B differs from the measurement patch 20 in that the transducer 44 and the transducer 45 are added. The transducer 44 and the transducer 45 are arranged in the center in the X direction, and together with the transducer 42, are arranged in a straight line parallel to the Y direction (corresponding to the second direction).

In this configuration, the blood flow measuring device uses the transducer 42, the transducer 44, and the transducer 45 to detect and correct the position of the measuring patch 20B in the width direction of the blood vessel 90. Then, the blood flow rate measuring device uses the transducer 41, the transducer 42, and the transducer 43 to detect and correct the position of the measuring patch 20B in the extending direction of the blood vessel 90.

As a result, the measurement patch 20B is arranged at the optimum position with respect to the optimum point PD in the blood vessel 90 without rotating the measurement patch 20B.

In the case of this configuration, the correction information in the X direction and the Y direction can be calculated at the same time, so that the correction can be notified in two dimensions. Therefore, in addition to the light emitting element 6121, the light emitting element 6122, the light emitting element 6131, and the light emitting element 6132 shown in the first embodiment, the measurement patch 20B is in the Y direction as shown in FIG. 13 (A). It is possible to provide a light emitting element 6141, a light emitting element 6142, a light emitting element 6151, and a light emitting element 6152 arranged side by side to perform notification. The arrangement of the plurality of light emitting elements 6141, light emitting element 6142, light emitting element 6151, and light emitting element 6152 arranged in the Y direction includes the light emitting element 6121, the light emitting element 6122, the light emitting element 6131, and the light emitting element 6132 arranged in the X direction. This can be achieved by rotating the array 90 °. Further, the notification unit may notify the correction information to be moved in an oblique direction (direction parallel to the diagonal line on the surface 201 of the measurement patch 20B).

(Configuration example of the second derivation)
As shown in FIG. 13B, the measurement patch 20C differs from the measurement patch 20 in that the transducer 42 is replaced with a plurality of transducers 403-409. A plurality of transducers 403-409 are arranged along the X direction.

In such a configuration, the blood flow measuring device can detect the approximate position of the measuring patch 20C with respect to the blood vessel 90 by using the plurality of transducers 403-409 as one transducer together with the transducer 41 and the transducer 43. Further, the blood flow measuring device can detect a more detailed position of the measurement patch 20C with respect to the blood vessel 90 by forming a plurality of ultrasonic waves at different positions in the X direction by the plurality of transducers 403-409.

(Configuration example of the third derivation)
As shown in FIG. 13C, the measurement patch 20D differs from the measurement patch 20C in that the transducer 41D and the transducer 43D are provided.

The transducer 41D is to be replaced from the transducer 41 and the transducer 43D is to be replaced from the transducer 43.

The area of the wavefront of the transducer 41D is larger than the area of the wavefront of the transducer 41. The area of the wavefront of the transducer 43D is larger than the area of the wavefront of the transducer 43.

Even with such a configuration, the measurement patch 20D can obtain the same action and effect as the measurement patch 20C. Further, the measurement patch 20D can narrow the directivity of the ultrasonic waves transmitted from the transducer 41D and the transducer 43D.

(Structure example of the fourth derivation)
As shown in FIG. 14, the measurement patch 20E differs from the measurement patch 20B in that it includes a plurality of transducers 401-411, transducers 41E, and transducers 43E. The plurality of transducers 401-411 are arranged at the center in the X direction and along the Y direction. The area of the wavefront of the transducer 41E is larger than the area of the wavefront of the transducer 41. The area of the wavefront of the transducer 43E is larger than the area of the wavefront of the transducer 43.

In this configuration, the blood flow measuring device uses a plurality of transducers 401-411 to detect and correct the position of the measuring patch 20E in the width direction of the blood vessel 90. Then, the blood flow measuring device uses the ultrasonic waves of the transducer 41E, the ultrasonic waves of the plurality of transducers 401-411 using a predetermined number of transducers, and the ultrasonic waves of the transducer 43E in the direction in which the blood vessel 90 extends. Used for detecting and correcting the position of.

As a result, the measurement patch 20E is arranged at the optimum position with respect to the optimum point PD in the blood vessel 90 without rotating the measurement patch 20E.

(Example of fifth derivative configuration)
FIG. 15A is a diagram showing another configuration example of the measurement patch, and FIGS. 15B and 15C are diagrams showing the arrangement state of the measurement patch with respect to the blood vessel.

As shown in FIG. 15A, in the measurement patch 20E2, the transducer 41E and the transducer 43E are omitted from the measurement patch 20E, and a plurality of transducers 401-411 are arranged in the X direction of the housing 200. The difference is that the transducer 51 and the transducer 52 are arranged in the Y direction of the housing 200.

In this configuration, as shown in FIG. 15B, if the measurement patch 20E2 is placed at the correct position with respect to the blood vessel 90, that is, if the transducer 51 and the transducer 52 overlap the blood vessel 90. Blood flow rate (blood flow rate) can be measured. On the other hand, as shown in FIG. 15C, if the arrangement direction of the transducer 51 and the transducer 52 and the extending direction of the blood vessel 90 are not parallel and the transducer 51 and the transducer 52 do not overlap the blood vessel 90, the blood flow volume. (Blood flow velocity) cannot be measured.

Therefore, by providing the configuration of the measurement patch E2, it can be easily determined from the measurement result of the blood flow velocity whether or not the measurement patch 20E2 is arranged at the correct position with respect to the blood vessel 90.

(Other configuration examples of the functional configuration of the blood flow rate measuring device)
16 and 17 are functional block diagrams of the blood flow rate measuring device.

(Example of first derived functional configuration)
As shown in FIG. 16, the blood flow rate measuring device 10F differs from the blood flow rate measuring device 10 in the arrangement position of the notification unit 60. Other configurations of the blood flow rate measuring device 10F are the same as those of the blood flow rate measuring device 10, and the description of the same parts will be omitted.

The notification unit 60 is provided on the main body 30F. With such a configuration, the measurement patch 20F can be made even smaller. Further, by providing the notification unit 60 on the main body 30F, which has less restrictions on the shape than the measurement patch 20, a wider variety of notification methods can be adopted.

(Example of second derivative function configuration)
As shown in FIG. 17, the blood flow rate measuring device 10G differs from the blood flow rate measuring device 10 in that it includes a communication control unit 33 and an antenna 330. Other configurations of the blood flow rate measuring device 10G are the same as those of the blood flow rate measuring device 10, and the description of the same parts will be omitted.

The blood flow rate measuring device 10G includes a main body 30G. The main body 30G includes a communication control unit 33 and an antenna 330. The communication control unit 33 is connected to the calculation unit 32. The antenna 330 is connected to the communication control unit 33.

The communication control unit 33 transmits the blood flow rate measured by the calculation unit 32 to an external computer (PC, smartphone, tablet device, etc.), a server device, or the like via the antenna 330. The communication control unit 33 may transmit the echo signal to an external computer, server device, or the like. In addition, the correction information in the X and Y directions is output to the connected external computer, and the external computer notifies the inspection target person or the inspection companion (attendant or medical staff) of the correction information. May be good.

(Other configuration examples of the notification unit)
FIG. 18A is a diagram showing another configuration example of the notification unit, and FIGS. 18B, 18C, and 18D are diagrams showing a notification example in the notification unit. FIG. 18E is a diagram showing a configuration example further derived from the notification unit.

As shown in FIG. 18A, the measurement patch 20G includes a light emitting element 611, a light emitting element 616A, a light emitting element 616B, a light emitting element 616C, a light emitting element 616D, a light emitting element 616E, a light emitting element 616F, a light emitting element 616G, and a light emitting element. It includes a 616H, a light emitting element 616I, a light emitting element 616J, a light emitting element 616K, and a light emitting element 616L. The housing 200 of the measurement patch 20G includes light emitting units for each of these light emitting elements 611 and 616A-616L. The light emitting portions of the light emitting elements 611 and 616A-616L and the light emitting portions for each of the light emitting elements 611 and 616A-616L are arranged so as to overlap each other with the surface 211 of the housing 200 viewed from the front. The other configurations of the measurement patch 20G are the same as those of the measurement patch 20, and the description of the same parts will be omitted.

As shown in FIG. 18A, the light emitting portion of the light emitting element 611 is arranged at the center of the surface 211 of the housing 200. The light emitting portions for each of the plurality of light emitting elements 616A-616L are sequentially arranged at equal intervals (about 30 ° in this example) on the circumference centered on the light emitting portion of the light emitting element 611 (origin).

A light emitting unit for each of the light emitting elements 611 and 616A-616L having such a configuration is provided. By including the light emitting elements 611, 616A-616L and the light emitting portion thereof, the measurement patch 20G can notify the rotation amount of the housing 200.

For example, in the case of FIG. 18B, the four light emitting elements 616A-616D emit light, and the other light emitting elements do not emit light. In this case, the measurement patch 20G exhibits a rotation of 71 ° to 105 °. Further, for example, in the case of FIG. 18C, the three light emitting elements 616A-616C emit light, and the other light emitting elements do not emit light. In this case, the measurement patch 20G exhibits a rotation of 36 ° to 70 °. Further, for example, in the case of FIG. 18D, the two light emitting elements 616A and 616B emit light, and the other light emitting elements do not emit light. In this case, the measurement patch 20G exhibits a rotation of 0 ° to 35 °.

It should be noted that all the light emitting elements to be light-emitting may be turned on at the same time, but for example, light may be emitted in order along an arc (in the order of arrangement) starting from 616A. Further, the light emitting elements that have been made to emit light may be quenched in order.

The rotation amount referred to here may be an angle at which the measurement patch 20G should be rotated for appropriate measurement, or may be an angle at which the measurement patch 20G is rotated. In the case of the angle to be rotated, for example, the deviation amount with respect to the normal position at the time of measurement of the measurement patch 20G is detected by using the ultrasonic measurement result or the posture sensor, and the rotation amount is obtained from this deviation amount. Should be decided. In this case, the person to be inspected or the companion of the inspection can easily recognize the amount of rotation to the normal position. Further, in the case of a rotated angle, the amount of rotation of the housing 200 of the measurement patch 20G may be measured using a posture sensor or the like. In this case, the inspection target person or the inspection companion can easily recognize the rotation amount of the housing 200.

The same effect can be obtained by using the measurement patch 20GA having the configuration shown in FIG. 18 (E). The measurement patch 20GA differs from the measurement patch 20G in that a plurality of light emitting elements 616E-616L are omitted. That is, the measurement patch 20GA includes a light emitting element 611 and a plurality of light emitting elements 616A, 616B, 616C, and 616D arranged on a 90 ° arc.

(Other examples of wearing the blood flow measuring device to the person to be inspected)
FIG. 19 is a perspective view showing another wearing state of the blood flow measuring device. In the case shown in FIG. 19, only the measurement patch 20 is attached to the neck 990 of the examinee 99. That is, as compared with the case shown in FIG. 2B described above, the configuration of FIG. 19 does not include the main body 30 and the cable 21. Such a configuration includes, for example, a built-in functional unit of the main body 30 in the measurement patch 20, connecting the measurement patch 20 and the main body 30 by wireless communication or the like, and providing a storage unit in the measurement patch 20. This can be realized by temporarily storing the echo signal in this storage unit and providing a communication port or the like capable of outputting the echo signal later. By providing such a configuration, it is possible to reduce the load, discomfort, etc. when the blood flow rate measuring device is attached to the person to be inspected 99. By attaching at least one measurement patch 20 to the neck, blood flow can be measured.

As shown in FIG. 19 and FIG. 2B described above, by attaching the two measurement patches 20 to the neck 990 of the inspection subject 99 substantially symmetrically, the following effects can be obtained. can get. With this configuration, the degree of stenosis and the difference between the left and right can be determined. Further, in this configuration, the accuracy of measurement can be improved. Further, in this configuration, for example, the amount of blood sent from the artificial heart-lung machine used during the operation can be grasped.

Further, in each of the above-described embodiments and derivative configurations, the notification unit is configured to notify the test subject or the test companion (attendant or medical worker) by light or sound, but is limited to this. It's not a thing. For example, it may be configured to notify the person to be inspected or the accompanying person (an attendant or a medical worker) of the examination by a tactile sensation such as vibration.

In addition, each of the above-described embodiments and derivative configurations can be appropriately combined, and the action and effect corresponding to each combination can be obtained.

10, 10F, 10G: Blood flow measuring device 20, 20A, 20B, 20C, 20D, 20E, 20F, 20G, 20GA: Measurement patch 21: Cable 30, 30F, 30G: Main body 31: Signal control unit 32: Calculation unit 33: Communication control unit 41, 41D, 41E, 42, 43, 43D, 43E, 44, 45, 51, 52, 401-411: Transducer 60: Notification unit 90, 91, 92: Blood vessel 99: Inspector 200: Housing 201: Front surface 202: Back surface 203, 204, 205, 206: Side surface 300: Battery 330: Antenna 400: Matching layer 611, 6121, 6122, 6131, 6132, 6141, 6142, 6151, 6152, 616A, 616B, 616C , 616D, 616E, 616F, 616G, 616H, 616I, 616J, 616K, 6161: Light emitting element 620: Sound emitting part 901: Skin surface 990: Neck part 991: Shoulder PD: Optimal point PJ: Branch point

Claims (14)

Each has a wavefront that transmits ultrasonic waves to the object to be inspected and receives echoes of the ultrasonic waves, and a plurality of transducers arranged in a first direction substantially parallel to the wavefront.
A calculation unit that detects the position of a blood vessel in the examination target in the first direction and generates position correction information from the difference in the time characteristics of the echo amplitudes of the plurality of transducers.
An inspection housing in which the plurality of transducers are arranged in the first direction and attached to the inspection object, and a housing for inspection.
A blood vessel position detector. A notification unit for notifying according to the correction information of the position is provided.
The blood vessel position detecting device according to claim 1. The plurality of transducers transmit ultrasonic waves having a predetermined directivity from the wavefront.
The calculation unit
The position of the blood vessel is detected by using the difference between the peak time at which the amplitude of the echo of the plurality of transducers peaks and the transmission time of the ultrasonic wave.
The blood vessel position detecting device according to claim 1 or 2. The calculation unit
The position of the blood vessel is detected by the position of the transducer that minimizes the difference between the peak time and the transmission time.
The blood vessel position detecting device according to claim 3. The calculation unit
A specific position in the extending direction of the blood vessel is detected by the position of the transducer having the minimum difference between the peak time and the transmission time.
The blood vessel position detecting device according to claim 4. A plurality of the plurality of transducers are arranged side by side in the second direction orthogonal to the first direction as well as in the first direction.
A specific position in the extending direction of the blood vessel is detected by the position of the transducer having the smallest difference between the peak time and the transmission time in the plurality of transducers arranged in the second direction.
The blood vessel position detecting device according to claim 5. The inspection housing has a detection surface facing the inspection object and has a detection surface.
The wavefront of the plurality of transducers is arranged on the detection surface.
The plurality of transducers include a first transducer, a second transducer, and a third transducer that are aligned in a straight line along the first direction.
The second transducer is located substantially in the center of the housing in the first direction.
The blood vessel position detecting device according to any one of claims 1 to 6. Each of the plurality of transducers has a strong directivity in a direction orthogonal to the wavefront, and transmits a plurality of superdirectional ultrasonic waves in which the positions of the centers of the directivity in the first direction are different.
The calculation unit
The position of the blood vessel is detected by using the difference between the first peak time and the second peak time at which the amplitude of the echo of the plurality of super-directional ultrasonic waves becomes high.
The blood vessel position detecting device according to claim 1 or 5. The calculation unit
The position of the blood vessel is detected by the position of the center of directivity of the ultrasonic wave that maximizes the difference between the first peak time and the second peak time.
The blood vessel position detecting device according to claim 8. The plurality of transducers are provided, and a measurement housing having a detection surface facing the inspection object is provided.
The wavefront of the plurality of transducers is arranged on the detection surface.
The plurality of transducers transmit a first super-directional ultrasonic wave, a second super-directional ultrasonic wave, and a third super-directional ultrasonic wave aligned in a straight line along the first direction.
The directional axis of the second super-directional ultrasonic wave is substantially at the center of the first direction of the housing.
The blood vessel position detecting device according to claim 8 or 9. Each configuration of the blood vessel position detecting device according to any one of claims 1 to 10 and
The first blood flow measurement transducer and the second blood flow measurement transducer,
A signal control unit that drives the first blood flow rate measuring transducer and the second blood flow rate measuring transducer in Doppler mode.
Equipped with
The calculation unit
The blood flow rate is measured from the measurement data of the first blood flow rate measuring transducer and the measurement data of the second blood flow rate measuring transducer.
Blood flow measuring device. The first blood flow rate measuring transducer and the second blood flow rate measuring transducer are arranged so as to sandwich the plurality of transducers in the first direction.
The blood flow rate measuring device according to claim 11. The first blood flow rate measuring transducer and the second blood flow rate measuring transducer are arranged so as to sandwich the arrangement position of the plurality of transducers in the second direction orthogonal to the first direction.
The blood flow rate measuring device according to claim 11. The transmission / reception surface of the first blood flow measurement transducer and the transmission / reception surface of the second blood flow measurement transducer are
It is tilted toward the side where the plurality of transducers are arranged at approximately 45 ° with respect to the wavefront of the plurality of transducers.
The blood flow rate measuring device according to any one of claims 11 to 13.

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