WO2016092679A1

WO2016092679A1 - Blood flow sensor

Info

Publication number: WO2016092679A1
Application number: PCT/JP2014/082886
Authority: WO
Inventors: 智夫五明; 英路平; 直人友安
Original assignee: 愛知時計電機株式会社
Priority date: 2014-12-11
Filing date: 2014-12-11
Publication date: 2016-06-16
Also published as: JPWO2016092679A1

Abstract

This blood flow sensor 1 can measure the flow speed of blood B passing through a transparent tube 40, and is provided with a light-emitting element 10 which emits a laser beam L, a reflective body 30 which reflects the beam L, and a light-receiving element 20 which receives light. The light-emitting element 10 emits the laser beam L in a direction that crosses the central axis 40a in a plane extending along the center axis 40a of the tube 40. The travelling beam L, emitted by the light-emitting element 10 and reflected by the tube 40, is reflected by the reflective body 30 in the direction opposite of the direction of travel. The light-receiving element 20 receives (non-Doppler-shifted) light of the beam L which has been reflected by the reflective body 30 and reflected again on the tube 40, and (Doppler-shifted) light of the beam L which has been emitted by the light emitting element 10 and reflected by a red blood cell R flowing through the tube 40.

Description

Blood flow sensor

In this specification, a technique related to a blood flow sensor is disclosed.

Patent Document 1 discloses a blood flow sensor that measures the flow velocity of blood flowing in a blood vessel in the body. The blood flow sensor includes a light emitting element, a light receiving element, and a control unit. This blood flow sensor is used in the vicinity of the human body, and the light emitting element emits laser light toward the body surface. A part of the laser light emitted from the light emitting element is reflected by the body surface, and the other part is reflected by red blood cells that enter the body and move in the blood vessel. The light receiving element receives light reflected by the body surface and light reflected by red blood cells. The former is reference light that is not subjected to the Doppler effect due to the blood flow velocity, and the latter is measurement light that is subject to the Doppler effect due to the blood flow velocity. The control unit analyzes the received light signal received by the light receiving element using a heterodyne technique, and calculates the flow rate of red blood cells. This type of blood flow sensor is called a laser Doppler blood flow sensor.

In the medical field, extracorporeal circulation is performed in which blood flowing through the body is sent out of the body and the blood sent out of the body is returned to the body again. In extracorporeal circulation, a transparent tube is used so that the blood state can be observed. The transparent tube is connected to a blood vessel inside the body, blood flowing through the blood vessel inside the body flows into the transparent tube outside the body, and the blood flowing through the transparent tube returns to the blood vessel inside the body.

JP 2008-272085 A

Even if the technique of Patent Document 1 is applied to blood flowing in a transparent tube, the flow velocity of blood flowing in the transparent tube cannot be measured. In the laser Doppler technology, it is necessary to receive both the reference light not subjected to the Doppler effect and the measurement light subjected to the Doppler effect, and to analyze the received light signal by the heterodyne technology. In Patent Document 1, since measurement is performed in an opaque body, a part of the laser light is reflected on the body surface, and reference light that is not subjected to the Doppler effect can be obtained. On the other hand, the tube used for extracorporeal circulation is transparent, and the reference light cannot be obtained without any ingenuity. Therefore, in the present specification, a technique is disclosed that makes it possible to obtain reference light that has not been subjected to the Doppler effect by using a reflector, thereby making it possible to accurately measure the blood flow velocity.

The blood flow sensor disclosed in this specification can measure the flow velocity of blood flowing in a transparent tube, and includes a light emitting element that emits laser light, a reflector that reflects light, and a light receiving element that receives light. I have. The light emitting element emits laser light in a direction crossing the central axis in a plane extending along the central axis of the transparent tube through which blood taken out of the body flows. In that case, a part of the laser beam is reflected at the interface between the transparent tube and blood (that is, the inner surface of the transparent tube). The reflector is disposed on the optical path of the reflected light, and reflects the reflected light in a direction opposite to the traveling direction of the reflected light. In the light receiving element, the light reflected by the reflector is reflected again by the transparent tube (light not subjected to the Doppler effect) and the light emitted from the light emitting element is reflected by the blood component flowing in the transparent tube. Receives light (light undergoing Doppler effect).

According to the above configuration, since the tube is transparent, the state of blood taken out from the body can be observed from the outside of the tube. A part of the laser light emitted from the light emitting element is reflected by the tube wall, reflected by the reflector, and again reflected by the tube wall and received by the light receiving element. Therefore, the light receiving element can receive a sufficient amount of reference light. At the same time, the measurement light reflected by the blood component can be received. Even if the tube through which the blood flows is transparent, it can receive a sufficient amount of reference light and a sufficient amount of measurement light necessary for detection in the heterodyne technology, and the flow rate of blood flowing in the transparent tube can be reduced. Accurate measurement.

It is sectional drawing of a blood flow sensor and a pipe | tube. FIG. 2 is a cross-sectional view taken along the line II-II in FIG. It is a top view of a blood flow sensor. It is a block diagram of a blood flow sensor. It is an enlarged view of the principal part V of FIG. It is sectional drawing of the blood-flow sensor and tube which concern on another Example. It is sectional drawing of the blood flow sensor which concerns on another Example, and a pipe | tube. It is sectional drawing of the blood flow sensor which concerns on another Example, and a pipe | tube.

The main features of the embodiment described below are listed. Note that the technical elements described below are independent technical elements, and exhibit technical usefulness alone or in various combinations.

(Feature 1) The reflecting surface of the reflector is formed in a concave shape. The amount of reference light can be increased.
(Feature 2) A transparent first light guide having a contact surface facing the outer surface of the tube is provided, and the refractive index of the first light guide is the same as the refractive index of the tube. The laser light emitted from the light emitting element is emitted from the contact surface of the first light guide and enters the tube. In this case, reflection on the outer wall of the transparent tube is suppressed, and a relationship of reflecting on the inner wall of the transparent tube can be obtained. The amount of light that reaches the reflector and is reflected by the reflector increases.
(Feature 3) A transparent second light guide is disposed between the first light guide and the tube. The refractive index of the second light guide is the same as the refractive index of the first light guide. The second light guide is in contact with the contact surface of the first light guide and the outer surface of the tube. In this case, only the second light guide can be exchanged. Only parts that are easily damaged can be replaced.
(Feature 4) The light emitting element and the light receiving element are fixed to the first light guide.
(Feature 5) The light emitting element, the light receiving element, and the reflector are all fixed to the first light guide.
(Feature 6) The contact surface of the first light guide is in contact with the outer surface of the tube.

(First embodiment)
Hereinafter, a first embodiment will be described with reference to the accompanying drawings. FIG. 1 illustrates a surface extending along the central axis 40a of the transparent tube 40 through which the blood B flows. As shown in FIGS. 1 to 3, the blood flow sensor 1 according to the embodiment includes a first light guide 50 and a second light guide 60. The blood flow sensor 1 includes a light emitting element 10, a light receiving element 20, and a reflector 30. As shown in FIG. 4, the blood flow sensor 1 includes a control unit 90 connected to the light emitting element 10 and the light receiving element 20.

As shown in FIGS. 1 to 3, the blood flow sensor 1 is used by being attached to a transparent tube 40 through which blood B flows. The blood flow sensor 1 is disposed outside the transparent tube 40. The blood flow sensor 1 can measure the flow velocity and flow rate of the blood B flowing through the transparent tube 40. In the following description, the blood flow sensor 1 will be described in a state where it is attached to the transparent tube 40 (hereinafter referred to as the tube 40).

The tube 40 includes a tube wall 41 and a flow path 42. A flow path 42 is formed in a space surrounded by the tube wall 41. The tube 40 is connected to a blood vessel (not shown) in the patient's body, and blood B flows into the tube 40 from the patient's blood vessel. The blood B flows through the flow path 42 along the central axis 40 a of the tube 40. The blood B flowing through the tube 40 is sent back to the patient's blood vessel again. Thus, the patient's blood B is once taken out of the patient's blood vessel and sent back to the patient's blood vessel, whereby blood B is extracorporeally circulated. Blood B contains various components. For example, blood B contains components such as red blood cells, white blood cells, platelets, plasma, and lymphocytes.

The tube wall 41 is made of, for example, transparent resin or glass. The tube wall 41 is light transmissive and can transmit the laser light L and visible light. Since the tube wall 41 is formed transparently, the inside of the tube wall 41 can be visually recognized through the tube wall 41, and the blood B flowing through the flow path 42 inside the tube wall 41 can be visually recognized. The flow path 42 extends along the central axis 40 a of the tube 40, and the blood B flows along the central axis 40 a of the tube 40. The cross-sectional shape of the tube 40 in the direction orthogonal to the central axis 40a of the tube 40 is not particularly limited. In the present embodiment, as shown in FIG. 2, the cross-sectional shape of the tube 40 in the direction orthogonal to the central axis 40a is a quadrangle.

The first light guide 50 is disposed so as to face the tube wall 41 of the tube 40. The first light guide 50 is made of, for example, transparent resin or glass. The first light guide 50 is formed solid. The first light guide 50 is light transmissive and can transmit the laser light L and visible light. The first light guide 50 is a light guide through which the laser light L passes.

The first light guide 50 has an entrance / exit surface 51, a reflection surface 52, and a contact surface 53. The entrance / exit surface 51 is formed in a planar shape. The inlet / outlet surface 51 is inclined with respect to the central axis 40 a of the tube 40, that is, the blood B flow direction. The entrance / exit surface 51 is formed so as to face obliquely upward on the upstream side in the flow direction of blood B. The reflection surface 52 is formed in a planar shape. The reflecting surface 52 is also inclined with respect to the central axis 40a of the tube 40, that is, the flow direction of the blood B. The reflection surface 52 is formed so as to face obliquely upward on the downstream side in the blood B flow direction. The entrance / exit surface 51 and the reflection surface 52 are formed at positions facing each other in the blood B flow direction. The entrance / exit surface 51 and the reflection surface 52 are formed so as to be opposite to each other in the axial direction of the tube 40. The entrance / exit surface 51 and the reflection surface 52 are formed at the same height position.

The contact surface 53 is formed to face the outer surface 43 of the tube 40. The contact surface 53 is formed to have a shape that matches the shape of the outer surface 43 of the tube wall 41 of the tube 40. The contact surface 53 is formed so as to extend along the central axis 40 a of the tube 40, that is, the blood B flow direction. A second light guide 60 is disposed between the contact surface 53 of the first light guide 50 and the outer surface 43 of the tube 40.

The second light guide 60 is made of, for example, transparent resin or glass. The second light guide 60 is light transmissive and can transmit the laser light L and visible light. The second light guide 60 is a light guide through which the laser light L passes. The second light guide 60 is in contact with the contact surface 53 of the first light guide 50 and the outer surface 43 of the tube 40. Grease (not shown) is applied between the second light guide 60 and the first light guide 50 and between the second light guide 60 and the tube 40. The second light guide 60 is in close contact with the first light guide 50 and the tube 40 via grease. The grease is light transmissive and can transmit the laser light L and visible light. The second light guide 60 is detachably attached to the first light guide 50. For example, the second light guide 60 is adhered to the first light guide 50 through adhesive grease, and is detached by being peeled off from the first light guide 50.

The second light guide 60 has an entrance / exit surface 61 and a contact surface 62. The entrance / exit surface 61 is in contact with the contact surface 53 of the first light guide 50. The entrance / exit surface 61 is formed to have a shape that matches the shape of the contact surface 53 of the first light guide 50. The contact surface 62 is formed to have a shape that matches the shape of the outer surface 43 of the tube wall 41 of the tube 40. The contact surface 62 is in contact with the outer surface 43 of the tube 40. The entrance / exit surface 61 and the contact surface 62 are formed so as to extend along the central axis 40a of the tube 40, that is, the blood B flow direction.

Since the first light guide 50, the second light guide 60, and the tube wall 41 of the tube 40 are formed transparently, the first light guide 50, the second light guide 60, and the tube wall 41 are used. The inside of the tube wall 41 can be visually recognized, and the state of the blood B flowing through the tube 40 can be grasped. The refractive index of the first light guide 50, the second light guide 50, the second light guide 60, and the refractive index of the first light guide 50 so that the light guides straight without being refracted when passing through the tube wall 41 of the tube 40. The refractive index of the light body 60 and the refractive index of the tube 40 are preferably the same. In addition, the refractive index of the 1st light guide 50, the 2nd light guide 60, and the pipe | tube 40 may mutually differ.

The light emitting element 10 is fixed to the entrance / exit surface 51 of the first light guide 50. The light emitting element 10 is covered with a cover 70. The light emitting element 10 emits laser light L. The laser light L emitted from the light emitting element 10 enters the first light guide 50 through the entrance / exit surface 51. As the light emitting element 10, for example, a laser diode (LD) can be used. The frequency of the laser beam L emitted from the light emitting element 10 is not particularly limited.

The light emitting element 10 emits laser light L toward the transparent tube 40 and blood B flowing through the tube 40. The light emitting element 10 emits laser light L from the outside of the tube 40 toward the inside of the tube 40. The light emitting element 10 irradiates the laser beam L toward the central axis 40a, that is, the direction intersecting the blood B flow direction, in a plane extending along the central axis 40a (the plane shown in FIG. 1). Further, the light emitting element 10 irradiates the laser light L toward the downstream side in the blood B flow direction. The light emitting element 10 irradiates the laser beam L obliquely downward. The light emitting element 10 irradiates the laser beam L at an angle such that the laser beam L incident on the tube 40 is not totally reflected by the inner surface of the tube 40.

The laser light L emitted from the light emitting element 10 passes through the first light guide 50, the second light guide 60 and the tube wall 41. The laser light L that has passed through the first light guide 50 exits from the contact surface 53 and enters the second light guide 60, and the laser light L that has passed through the second light guide 60 exits from the contact surface 62. Incident on the tube wall 41. Part of the laser light L that has passed through the tube wall 41 is reflected at the boundary between the tube wall 41 and the flow path 42 (the inner surface of the tube wall 41). The laser beam L reflected at the boundary between the tube wall 41 and the flow path 42 is reflected to change the traveling direction and travel toward the reflector 30. Laser light traveling toward the reflector 30 passes through the tube wall 41, the second light guide 60, and the first light guide 50. The laser light L that has passed through the first light guide 50 is incident on the reflector 30.

The reflector 30 is fixed to the reflecting surface 52 of the first light guide 50. The reflector 30 reflects the laser light L incident on the reflector 30. As the reflector 30, a mirror that reflects light can be used. The reflector 30 has a reflecting surface 31 and reflects light by the reflecting surface 31. The reflection surface 31 is a flat surface. The reflection surface 31 of the reflector 30 is fixed to the reflection surface 52 of the first light guide 50. The reflector 30 reflects the laser light L in the direction opposite to the traveling direction of the incident laser light L. If the angle between the traveling direction of the laser light L emitted from the light emitting element 10 and the central axis 40a of the tube 40 is θ, the traveling direction of the laser light L reflected by the reflector 30 and the central axis 40a of the tube 40 form. The angle is 180 ° -θ. The laser beam L reflected by the reflector 30 travels in the direction opposite to the traveling direction. The reflector 30 reflects the laser light L traveling in a direction inclined with respect to the blood B flow direction. That is, the reflector 30 reflects the laser light L traveling along a direction inclined with respect to the central axis 40 a of the tube 40. The reflector 30 reflects the laser light L toward the upstream side in the blood B flow direction. The reflector 30 reflects the laser light L obliquely downward.

The laser light L reflected by the reflector 30 passes through the first light guide 50, the second light guide 60 and the tube wall 41. The laser light L that has passed through the tube wall 41 is reflected at the boundary between the tube wall 41 and the flow path 42 (the inner surface of the tube wall 41). The laser light L reflected at the boundary between the tube wall 41 and the flow path 42 is reflected to change the traveling direction and travel toward the light receiving element 20. The laser light L traveling toward the light receiving element 20 passes through the tube wall 41, the second light guide 60 and the first light guide 50. The laser light L that has passed through the first light guide 50 is emitted from the entrance / exit surface 51 of the first light guide 50 and is received by the light receiving element 20.

The light receiving element 20 is fixed to the entrance / exit surface 51 of the first light guide 50. The light receiving element 20 is disposed next to the light emitting element 10. The light receiving element 20 is covered with a cover 70. The light receiving element 20 receives light incident on the light receiving element 20 and outputs an electrical signal corresponding to the received light quantity. A photodiode (PD) can be used for the light receiving element 20. The light receiving element 20 receives the laser light L traveling along the direction inclined with respect to the central axis 40 a of the tube 40. The light receiving element 20 receives the laser light L traveling backward in the blood B flow direction. The light receiving element 20 receives the laser light L traveling obliquely upward.

The cover 70 is fixed to the first light guide 50. The cover 70 has a light shielding property. The cover 70 is configured so that light does not enter the light emitting element 10 and the light receiving element 20 from the outside.

Part of the laser light L emitted from the light emitting element 10 enters the flow path 42 after passing through the first light guide 50, the second light guide 60, and the tube wall 41. Thereby, a part of the laser light L emitted from the light emitting element 10 enters the blood B flowing through the flow path 42.

As shown in FIG. 5, the laser light L incident on the flow path 42 from the boundary between the tube wall 41 and the flow path 42 travels in the blood B. The laser light L incident on the flow path 42 is refracted at the boundary between the tube wall 41 and the flow path 42. The laser light L incident on the flow path 42 proceeds in a direction inclined with respect to the flow direction of the blood B flowing through the tube 40. The laser light L traveling in the blood B strikes and reflects the components contained in the blood B. Specifically, the laser light L strikes and reflects the red blood cells R contained in the blood B, and the reflected light S is generated. By reflecting on the moving red blood cell R, the frequency of light changes before and after the reflection. Therefore, the frequency of the laser light L and the frequency of the reflected light S are different. The reflected light S travels in a direction opposite to the direction in which the laser light L travels in the blood B. The reflected light S traveling in the blood B in the direction opposite to the laser light L is emitted from the boundary between the flow path 42 and the tube wall 41 to the tube wall 41. The reflected light S emitted to the tube wall 41 is refracted at the boundary between the flow path 42 and the tube wall 41.

As shown in FIG. 1, the reflected light S emitted to the tube wall 41 travels in a direction opposite to the direction in which the laser light L emitted from the light emitting element 10 travels. The light passes through the tube wall 41, the second light guide 60, and the first light guide 50 and proceeds toward the light receiving element 20. That is, the reflected light S reflected by the red blood cells R travels toward the light receiving element 20. The reflected light S that has passed through the first light guide 50 exits from the entrance / exit surface 51 of the first light guide 50. When the reflected light S is emitted from the entrance / exit surface 51, the light receiving element 20 receives the reflected light S. The reflected light S received by the light receiving element 20 is used for calculating the flow velocity of the blood B flowing through the tube 40.

The light receiving element 20 receives light reflected by the reflector 30 (reference light not receiving the Doppler effect) and light reflected by the red blood cells R (measurement light receiving the Doppler effect). The control unit 90 calculates the frequency difference between the reference light and the measurement light using the heterodyne technique, and calculates the blood flow rate from the calculation result.

As shown in FIG. 4, the control unit 90 is connected to the light emitting element 10 and the light receiving element 20. The control unit 90 controls the light emitting element 10 and the light receiving element 20. The controller 90 calculates the flow velocity of the blood B flowing through the tube 40 based on the light received by the light receiving element 20. Further, the control unit 90 calculates the flow rate of blood B. The control unit 90 performs calculation using a heterodyne technique. In the heterodyne technique, a beat (beat) generated by overlapping two waves (light) having different frequencies is analyzed, and a frequency difference between the two waves (light) is calculated. Since the heterodyne technique is known, a detailed description is omitted. The control unit 90 outputs the calculated blood B flow velocity and flow rate to a monitor (not shown).

As is clear from the above description, the blood flow sensor 1 can measure the flow velocity of the blood B flowing through the transparent tube 40, the light emitting element 10 that emits the laser light L, and the reflector that reflects the light. 30 and a light receiving element 20 for receiving light. The light emitting element 10 emits laser light L along the direction inclined with respect to the axial direction of the tube 40 toward the blood B flowing in the transparent tube 40. The reflector 30 reflects the light that travels when the laser light L emitted from the light emitting element 10 is reflected by the tube 40 in the direction opposite to the traveling direction. The light receiving element 20 reflects the light reflected by the reflector 30 again by the tube 40, and the light reflected by the red blood cells R in the blood B when the laser light L emitted from the light emitting element 10 enters the blood B. The light S is received. According to such a configuration, since the blood B flows in the transparent tube 40, the blood B in the tube 40 can be visually recognized from the outside, and the state of the blood B can be grasped from the outside. it can. Further, a part of the laser light L emitted from the light emitting element 10 is reflected by the tube 40. Then, the laser beam L reflected by the tube 40 is reflected by the reflector 30. Thereby, the laser light L emitted from the light emitting element 10 is reflected by the tube 40 and the reflector 30 and returns to the original position. As a result, the laser light L emitted from the light emitting element 10 can be reflected from the tube 40 and the reflector 30 and travel toward the light receiving element 20. Further, another part of the laser light L emitted from the light emitting element 10 enters the blood B in the tube 40 and is reflected by the red blood cells R in the blood B. The reflected light S reflected by the red blood cells R travels toward the light receiving element 20. Thereby, the light receiving element 20 can sufficiently receive light necessary for calculating the flow velocity of the blood B. That is, since the laser light L emitted from the light emitting element 10 can be used as light for calculating the flow velocity of the blood B, sufficient light necessary for calculating the flow velocity of the blood B can be obtained. Therefore, when calculating the flow velocity of the blood B flowing through the tube 40, it can be calculated with high accuracy. Therefore, even if the tube 40 through which the blood B flows is transparent, the flow rate of the blood B flowing through the tube 40 can be accurately measured.

Further, according to the blood flow sensor 1 described above, a part of the laser light L emitted from the light emitting element 10 enters the blood B in the tube 40. The laser beam L is incident and travels in a direction inclined with respect to the axial direction of the tube 40, that is, in a direction inclined with respect to the blood B flow direction. Laser light L traveling in a direction inclined with respect to the flow direction of blood B strikes red blood cells R included in blood B. Since the laser light L travels in a direction inclined with respect to the flow direction of the blood B, the blood flow velocity causing the Doppler effect is a blood velocity component in the direction along the traveling direction of the laser light. By using the trigonometric function, the blood speed in the direction along the central axis 40a can be converted. Further, by reducing the angle θ formed by the traveling direction of the laser light L emitted from the light emitting element 10 and the central axis 40a of the tube 40, the velocity component of the blood B along the traveling direction of the laser light L can be increased. it can. Thereby, the difference between the velocity of the laser beam L and the flow velocity of the blood B in the flow direction of the blood B can be increased. As a result, the Doppler shift can be increased, and the flow rate measurement accuracy can be increased.

In addition, since the second light guide 60 is disposed between the first light guide 50 and the tube 40, the contact surface 53 of the first light guide 50 can be protected. In the blood flow sensor 1 described above, the portion that comes into contact with the tube 40 is most easily damaged. Therefore, the second light guide 60 is damaged when the second light guide 60 is disposed in that portion. In this case, since the second light guide 60 can be attached to and detached from the first light guide 50, the blood flow sensor 1 can be easily repaired by replacing only the second light guide 60. Moreover, since it is not necessary to exchange parts other than the 2nd light guide 60, the blood flow sensor 1 can be repaired easily.

Further, if the refractive indexes of the light of the first light guide 50, the second light guide 60, and the tube 40 are the same, the first light guide 50, the second light guide 60, and the light are not refracted. Pass through tube 40. Further, it is possible to reduce light reflected at each boundary. Thereby, the light receiving element 20 can receive light sufficiently.

As mentioned above, although one Example was described, a specific aspect is not limited to the said Example. In the following description, the same components as those described above are denoted by the same reference numerals and description thereof is omitted.

(Second embodiment)
In the said Example, although the reflective surface 31 of the reflector 30 was a flat structure, it is not limited to this structure. In 2nd Example, as shown in FIG. 6, the reflective surface 31 of the reflector 30 may be a concave surface. The reflecting surface 31 is curved obliquely upward. In this case, the reflecting surface 52 of the first light guide 50 is a convex surface. Since the reflecting surface 31 of the reflector 30 is formed in a concave shape, the laser light L reflected by the reflecting surface 31 can be collected at the center. Thereby, since the laser beam L is collected at the center, the strong laser beam L can be incident on the light receiving element 20. Therefore, the light receiving element 20 can sufficiently obtain light necessary for calculating the flow velocity of the blood B.

(Third embodiment)
In the said Example, although the 2nd light guide 60 was arrange | positioned between the 1st light guide 50 and the pipe | tube 40, it is not limited to this structure. In the third embodiment, as shown in FIG. 7, the second light guide 60 may be omitted from between the first light guide 50 and the tube 40. In this case, the contact surface 53 of the first light guide 50 contacts the outer surface 43 of the tube 40. Grease (not shown) may be applied between the contact surface 53 of the first light guide 50 and the outer surface 43 of the tube 40.

(Fourth embodiment)
In the said Example, although the entrance / exit surface 51 and the reflective surface 52 of the 1st light guide 50 were formed in the same height position, it is not limited to this structure. In the fourth embodiment, as shown in FIG. 8, the entrance / exit surface 51 and the reflection surface 52 of the first light guide 50 are formed at different height positions. Therefore, the light emitting element 10 and the reflector 30 are disposed at different height positions. Further, the light receiving element 20 and the reflector 30 are arranged at different height positions. Even in such a configuration, the laser light L emitted from the light emitting element 10 enters the reflector 30, and the laser light L reflected by the reflector 30 enters the light receiving element 20.

In the above embodiment, the first light guide 50 is solid, but the present invention is not limited to this configuration. In another embodiment, a space may be formed in the first light guide 50. In this case, light travels through the space. Even in such a configuration, the laser light L emitted from the light emitting element 10 enters the reflector 30, and the laser light L reflected by the reflector 30 enters the light receiving element 20.

Specific examples of the present invention have been described in detail above, but these are merely examples and do not limit the scope of the claims. The technology described in the claims includes various modifications and changes of the specific examples illustrated above. The technical elements described in this specification or the drawings exhibit 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 technology exemplified in this specification or the drawings can achieve a plurality of objects at the same time, and has technical usefulness by achieving one of the objects.

DESCRIPTION OF SYMBOLS 1; Blood flow sensor 10; Light emitting element 20; Light receiving element 30; Reflector 31; Reflecting surface 40; Tube 40a; 52; reflective surface 53; contact surface 60; second light guide 61; entry / exit surface 62; contact surface 70; cover 90; controller B; blood L; laser light R;

Claims

A blood flow sensor capable of measuring the flow velocity of blood flowing in a transparent tube,
A light emitting element that emits laser light;
A reflector that reflects light;
It has a light receiving element that receives light,
The light emitting element emits laser light in a direction intersecting the central axis in a plane extending along the central axis of the tube;
The reflector reflects the reflected light that travels by the light emitted from the light emitting element being reflected by the tube in a direction opposite to the traveling direction of the reflected light,
The light receiving element reflects light that has not been subjected to the Doppler effect in which light reflected by the reflector is reflected again by the tube and light components that are emitted from the light emitting element are reflected by blood components flowing through the tube. To receive light that has received the Doppler effect,
A blood flow sensor characterized by the above.
The blood flow sensor according to claim 1, wherein the reflecting surface of the reflector is formed in a concave shape.
A transparent first light guide having a contact surface facing the outer surface of the tube;
The refractive index of the first light guide is the same as the refractive index of the tube;
The blood flow sensor according to claim 1 or 2, wherein a laser beam emitted from the light emitting element is emitted from the contact surface of the first light guide and is incident on the tube.
A transparent second light guide disposed between the first light guide and the tube;
The refractive index of the second light guide is the same as the refractive index of the first light guide;
The blood flow sensor according to claim 3, wherein the second light guide is in contact with the contact surface of the first light guide and an outer surface of the tube.