Sensor device

The present invention relates to a sensor device including an optical fiber type pressure sensor attached to an elongated support member such as a catheter or a guide wire.

Conventionally, a sensor device in which a pressure sensor is incorporated at the tip of an elongated support member such as a catheter or a guide wire is known in order to measure pressure in a relatively narrow place such as in a patient's blood vessel (Non-Patent Document 1). ). In such a sensor device, for example, a piezoresistive element is used as a pressure sensor. According to the sensor device having such a configuration, when the pressure sensor reaches the blood vessel constriction portion by inserting an elongated support member such as the catheter or the guide wire into the blood vessel of the patient, the pressure due to the blood vessel constriction portion is reached. Can be detected.

In addition, by providing a pressure sensor at the tip of the catheter, guide wire, etc., the internal state of the blood vessel, etc. can be adjusted to some extent based on the change in pressure detected by the pressure sensor when the pressure sensor is inserted into the blood vessel, etc. of the patient. Can be grasped. Similarly, for example, by providing a pressure sensor at the tip of the endoscope, when it is inserted into an organ such as the gastrointestinal tract of a patient, it can be used as a force sensor or a tactile sensor based on the change in pressure detected by the pressure sensor. It can be used to improve safety by measuring hardness and preventing excessive force. Such force sensors or tactile sensors are disclosed in, for example, Non-Patent Document 2 and Non-Patent Document 3.<nplcit num="1"><text>E. Kalvesten, L. Smith, L. Tenerz and G. Stemme, "The first surface micromachined pressure sensor for cardiovascular pressure measurements" Proc. Of IEEE International Workshop on Micro Electro Mechanical Systems (MEMS 98), 1998, pp.574- 579</text></nplcit><nplcit num="2"><text>M. Tanimoto, F. Arai, T. Fukuda, H. Iwata, Y. Gotoh, M. Hashimoto, and M. Negoro "MICRO FORCE SENSOR FOR INTRAVASCULAR NEUROSURGERY AND IN VIVO EXPERIMENT" Proc. Of IEEE International Workshop on Micro Electro Mechanical Systems (MEMS 98), 1998, pp.504-509</text></nplcit><nplcit num="3"><text>Mineyuki Haruta, Yoshinobu Murayama, Sadao Omata, "Research on Multifunctional Catheter for Hardness Measurement" 41st Annual Meeting of the Japan Society of ME &amp; BE (May 2002) p.65 Volume 40 Special issue</text></nplcit>

<p> However, in the sensor devices according to Non-Patent Documents 1 to 3, it is difficult to incorporate the piezoresistive element or the piezoelectric element near the tip of the support member, and the pressure measurement position is located relatively far from the tip of the support member. In addition, since the structure of the pressure sensor itself is complicated, the portion where the pressure sensor is incorporated in the support member such as the catheter or the guide wire becomes thick, and it is difficult to put it into practical use.</p><p> In this way, a pressure sensor can be incorporated into a support member such as a catheter, a balloon catheter, a guide wire, or an endoscope to detect pressure or force, or to be used as a tactile sensor, or a plurality of pressure sensors. When the flow velocity of blood is measured based on the pressure difference due to the pressure sensor, the built-in portion of the pressure sensor becomes thick, which limits the part where the support member can be inserted and puts a burden on the patient.</p><p> Further, when the temperature is also measured at the same time, for example, it is necessary to incorporate a thermocouple, and the pressure sensor incorporated portion of the support member becomes even thicker.</p><p> In view of the above points, the present invention can reach a narrow part, which has been difficult to insert in the past, by making it simple and compact, enabling precise measurement of a local part of the body and giving a burden to a patient or the like as much as possible. It is an object of the present invention to provide a sensor device that is eliminated.</p>

<p> According to the present invention, the above object is that the elongated support member, the optical fiber embedded in the support member along the longitudinal direction, and the periphery so as to define an internal space with respect to the tip surface of the optical fiber. It is provided with an optical fiber type pressure sensor including a diaphragm mounted in close contact and a reflective layer provided on the inner surface of the diaphragm, and the outer surface of the diaphragm of the pressure sensor is exposed to the outside. Achieved by the sensor device.</p><p> The sensor device according to the present invention preferably has a window portion that exposes the pressure sensor to the side on the outer surface of the support member corresponding to the pressure sensor.</p><p> In the sensor device according to the present invention, preferably, the outer surface of the diaphragm of the pressure sensor is exposed to the outside from the tip of the support member. In this case, the outer surface of the diaphragm exposed to the outside of the pressure sensor may be covered with an elastic material.</p><p> In the sensor device according to the present invention, preferably, the support member is formed in an elongated hollow cylindrical shape, and the optical fiber and the pressure sensor are provided in the peripheral wall portion of the support member.</p><p> In the sensor device according to the present invention, the support member may be a hollow catheter or a balloon catheter, or may be a guide wire or an endoscope.</p><p> The sensor device according to the present invention preferably includes a plurality of sets of optical fibers and pressure sensors, and each pressure sensor is arranged at a different position in the longitudinal direction in the support member.</p><p> The sensor device according to the present invention is preferably arranged so as to face an optical fiber embedded in the support member along the longitudinal direction and a window portion attached to the tip surface of the optical fiber and opened to the side of the support member. A first pressure sensor, an optical fiber embedded along the longitudinal direction in the support member, and a second pressure sensor attached to the tip surface of the optical fiber and exposed from the tip of the support member. It has.</p><p> The sensor device according to the present invention preferably applies pressure to each of the above pressure sensors based on the characteristics of interference light due to the phase shift of the reflected light on the front surface of the optical fiber and the reflective layer generated by the deformation of the diaphragm due to the external pressure. To detect.</p><p> The sensor device according to the present invention preferably changes the pressure of each of the above pressure sensors based on the characteristics of the interference light due to the phase shift of the reflected light on the front surface of the optical fiber and the reflective layer generated by the deformation of the diaphragm due to the external pressure. Detects the force due to.</p><p> The sensor device according to the present invention preferably refers to the first pressure sensor and the second pressure sensor, in which interference light is caused by a phase shift of the reflected light on the front surface of the optical fiber and the reflective layer generated by deformation of the diaphragm due to external pressure. The flow velocity is detected by the difference in pressure based on the characteristics of.</p><p> The sensor device according to the present invention preferably detects the temperature change that causes the pressure change based on the pressure change due to the temperature change in the internal space inside the diaphragm with respect to the pressure sensor.</p>

<p> According to the above configuration, when the outer surface of the diaphragm of the pressure sensor exposed to the outside of the support member is deformed inward based on the elasticity of the diaphragm by receiving pressure from the outside, the pressure sensor is prepared for the inner surface of the diaphragm of the incident light to the optical fiber. Since the phases of the reflected light by the reflected reflective layer and the reflected light on the tip surface of the optical fiber are different, the amount of movement of the diaphragm is detected, and the pressure is calculated based on this amount of movement.</p><p> In this case, since the sensor device is configured by embedding an optical fiber along the inside of the support member and attaching an optical fiber type pressure sensor to the tip of the optical fiber, the pressure sensor itself is very large, for example, about 125 μm in diameter. Since it can be configured to be compact, the external dimensions of the support member are hardly large even in the portion where the pressure sensor of the support member is incorporated. Therefore, when such a support member is inserted into, for example, a blood vessel of a patient, it can be inserted into a narrower part, the burden on the patient is reduced, and the sensor is inexpensive due to a simple configuration. The device can be configured.</p><p> When the outer surface of the support member corresponding to the pressure sensor is provided with a window portion that exposes the pressure sensor to the side, the pressure sensor externally opens the window portion that opens to the side of the support member. The pressure can be detected. At that time, since the pressure sensor is attached to the tip of the optical fiber embedded in the support member, it can be arranged near the tip of the support member, so that it is possible to detect the pressure near the tip of the support member. is there.</p><p> When the outer surface of the diaphragm of the pressure sensor is exposed to the outside from the tip of the support member, the pressure sensor exposed to the outside from the tip of the support member can detect the pressure outside the tip of the support member. it can. Therefore, for example, by calculating the force from the pressure detected by the pressure sensor, the force applied to the tip of the support member can be detected, and when the support member is inserted into a blood vessel, for example, the support member is obstructed. You can see how to hit things.</p><p> When the outer surface of the diaphragm exposed to the outside of the pressure sensor is covered with an elastic material, the pressure sensor exposed at the tip of the support member, for example, when the support member is inserted into a blood vessel of a patient. The outer surface of the diaphragm does not hit the blood vessel wall or the like and damage it.</p><p> When the support member is formed in an elongated hollow cylindrical shape and the optical fiber and the pressure sensor are provided in the peripheral wall portion of the support member, a guide wire may be inserted through the hollow portion of the support member, or the guide wire may be inserted. A chemical solution or the like can be flowed, and the pressure on the side of the support member can be detected by the pressure sensor.</p><p> When the support member is a hollow catheter or a balloon catheter, these catheters or balloon catheters can be inserted into, for example, a patient's blood vessel to perform a predetermined operation, and at the same time, the internal pressure and force are measured. be able to.</p><p> When the support member is a guide wire, the guide wire can be inserted into, for example, a blood vessel of a patient to perform a predetermined operation, and blood pressure can be detected at the time of insertion, reducing the burden on the patient. However, it becomes possible to insert it more safely.</p><p> When the support member is an endoscope, when the endoscope is inserted into the gastrointestinal tract of a patient, the endoscope measures the hardness by detecting the pressure on the wall of the gastrointestinal tract or the like. It is possible to perform the procedure, reduce the burden on the patient, and perform the insertion more safely.</p><p> A plurality of sets of optical fibers and pressure sensors are provided, and when each pressure sensor is arranged at a different position in the longitudinal direction in the support member, for example, when the support member is inserted into a patient's blood vessel, Based on the pressure detected by each pressure sensor, the pressure distribution around the vascular constriction can be detected at the same time.</p><p> Further, a first pressure sensor attached to the tip surface of the optical fiber and arranged facing the window opened to the side of the support member, and a second pressure sensor attached to the tip surface of the optical fiber and exposed from the tip of the support member. When the pressure sensor is provided, the pressure can be detected at the tip of the support member and a position in front of the tip by a predetermined distance.</p><p> For each of the above pressure sensors, when the pressure is detected based on the characteristics of the interference light due to the phase shift of the reflected light on the front surface of the optical fiber and the reflective layer generated by the deformation of the diaphragm due to the external pressure, the reflected light of each The pressure on the outer surface of the diaphragm can be detected from the phase shift.</p><p> For each of the above pressure sensors, when detecting the force due to pressure change based on the characteristics of the interference light due to the phase shift of the reflected light on the front surface of the optical fiber and the reflective layer generated by the deformation of the diaphragm due to external pressure, The force on the outer surface of the diaphragm can be detected from the phase shift of the reflected light.</p><p> Regarding the first pressure sensor and the second pressure sensor, due to the pressure difference, based on the characteristics of the interference light due to the phase shift of the reflected light on the front surface of the optical fiber and the reflective layer generated by the deformation of the diaphragm due to the external pressure. When detecting the flow velocity, for example, the flow velocity of blood in the blood vessel into which the support member is inserted can be detected based on the pressure difference between the tip of the support member and the position at a predetermined distance from the tip.</p><p> Regarding the above pressure sensor, when detecting a temperature change that causes a pressure change based on a pressure change due to a temperature change in the internal space inside the diaphragm, the temperature change of a gas such as air sealed in the diaphragm due to the temperature change is performed. The temperature outside the diaphragm can be detected based on the pressure change caused by the thermal expansion or contraction.</p><p> In this way, according to the present invention, by embedding an optical fiber having a small pressure sensor attached to the tip in the support member, the pressure near the tip of the support member or the like is detected with almost no change in the outer shape of the support member. can do. Therefore, it is possible to detect various measured values at a relatively low cost by detecting the pressure without imposing a heavy burden on the patient and further calculating the force, the flow velocity, the temperature, etc. from the pressure. It enables direct measurement of pressure in minute areas that were difficult to measure.</p>

Hereinafter, the present invention will be described in detail based on some embodiments shown in the drawings. 1 to 3 show a first embodiment of the sensor device according to the present invention. In FIG. 1, the sensor device 10 includes an elongated hollow cylindrical catheter 11, an optical fiber 12 embedded along the longitudinal direction in the peripheral wall of the catheter 11, and a pressure sensor 13 attached to the tip of the optical fiber 12. It is composed of.

The catheter 11 has a known structure, for example, is made of a silicone tube, and is selected to have an outer diameter of 1 mm and a wall thickness of 0.3 mm, for example. Then, as shown in FIGS. 2 and 3, the catheter 11 includes a through hole 11a extending in the longitudinal direction for receiving the optical fiber 12 in the peripheral wall. The through hole 11a opens laterally near the tip of the catheter 11 to define the window portion 11b.

The optical fiber 12 has a known configuration, for example, has an outer diameter of 125 μm, is inserted into the through hole 11a of the catheter 11, is embedded, and the tip thereof is lateral to the through hole 11a of the catheter 11. It is located facing the window 11b that opens to.

The pressure sensor 13 is, for example, an optical pressure sensor disclosed in Japanese Patent Application Laid-Open No. 2000-35369, and is formed on the diaphragm 13a and the inner surface near the center of the diaphragm 13a as shown in FIG. It is composed of a reflective layer 13b made of a metal thin film such as aluminum and a spacer 13c attached to the inner surface around the diaphragm 13. Specifically, the pressure sensor 13 is, for example, SiO.₂On the inner surface of the center of a diaphragm 13a having a diameter of 120 μm and a thickness of 0.7 μm.₂A reflective layer 13b made of an aluminum thin film having a thickness of about 0.2 to 0.5 μm is formed through a thick film mesa portion 13d having a diameter of 60 μm and a thickness of 2.3 μm, and a thickness of 2 is formed on the inner surface around the diaphragm 13a. It is constructed by forming a spacer 13c made of a polyimide thick film having a thickness of about 5 μm.

Then, the pressure sensor 13 having such a configuration is closely joined to the tip surface of the optical fiber 12 by using the spacer 13c as an adhesive layer. As a result, the internal space between the diaphragm 13a and the tip surface of the optical fiber 12 is sealed. A half mirror layer 12a is formed in advance on the tip surface of the optical fiber 12. The half mirror layer 12a is composed of, for example, a thin film of ZnS or Cr.

As a result, the pressure sensor 13 constitutes a so-called Fabry-Perot interferometer together with the half mirror layer 12a on the tip surface of the optical fiber 12, and causes white light to be incident on the other end of the optical fiber 12 from the light source. As shown in FIG. 4, the light L1 reflected by the half mirror 12a on the tip surface of the optical fiber 12 and the light transmitted through the half mirror 12a on the tip surface of the optical fiber 12 and reflected by the reflection layer 13b of the pressure sensor 13. It is modulated based on the optical path difference of L2 and returns in the optical fiber 12 again. Then, when the position of the diaphragm 13a changes due to the pressure acting on the diaphragm from the outside, the optical path difference also changes, so that the peak wavelength of the spectrum modulated as described above changes. Therefore, the pressure acting on the diaphragm can be measured by detecting the change in the peak wavelength with a spectroscope.

The sensor device 10 according to the embodiment of the present invention is configured as described above, and when used, the catheter 11 of the sensor device 10 is inserted into the blood vessel 14 of the patient, for example, as shown in FIG. Then, when the window 11b near the tip of the catheter 11 passes through the narrowed portion 14a of the blood vessel 14, the pressure changes before and after the narrowed portion 14a of the blood vessel, so that the pressure change can be detected by the pressure sensor 13.

In this case, since the pressure sensor 13 is compactly configured and fits within the tip surface of the optical fiber 12, even if the optical fiber 12 is embedded in the catheter 11, the outer diameter of the catheter 11 does not become large.

Further, by utilizing the fact that the internal space between the diaphragm 13a of the pressure sensor 13 and the tip surface of the optical fiber 12 is sealed, the atmospheric pressure due to thermal expansion or contraction of air or the like enclosed in this internal space is measured. By detecting the change with the pressure sensor 13, it is also possible to know the temperature outside the pressure sensor 13. In this way, the pressure sensor 13 can also be used as a temperature sensor.

FIG. 6 shows a second embodiment of the sensor device according to the present invention. In FIG. 6, the sensor device 20 has almost the same configuration as the sensor device 10 shown in FIGS. 1 to 3, but has a different configuration in that a balloon catheter 21 is used instead of the catheter 11. .. Here, the balloon catheter 21 is provided with an inflatable balloon 22 in a predetermined section near the tip, and is shown by a dotted line in FIG. 6, for example, when air is injected through an air pipe (not shown). It expands in the radial direction as shown. As shown in FIG. 6A, the pressure sensor 13 is exposed to the internal space of the balloon 22 through the window portion 21a provided on the peripheral surface of the catheter 21. Alternatively, the balloon 22 is exposed to the outside through the window portion 21a in front of the balloon 22 (see FIG. 6 (B)) or behind (see FIG. 6 (C)).

According to the sensor device 20 having such a configuration, for example, as shown in FIG. 7A, the catheter 21 of the sensor device 20 is inserted into the blood vessel (the aortic wall in the figure) 23 of the patient. Then, as shown in FIG. 7B, by inflating the balloon 22 of the catheter 21, the outer peripheral surface of the balloon 22 expands the blood vessel 23, and the volume of the balloon 22 is pushed into the peripheral arteries including the coronary arteries. It works. At that time, as shown in FIG. 6A, when the pressure sensor 13 is exposed in the internal space of the balloon 22, the pressure sensor 13 monitors the internal pressure of the balloon 22 at the time of expansion to be more precise. The internal pressure of the balloon can be controlled. Further, as shown in FIG. 6B or FIG. 6C, when the pressure sensor 13 is arranged before and after the balloon 22, the blood pressure before and after the balloon can be measured.

FIG. 8 shows a third embodiment of the sensor device according to the present invention. In FIG. 8, the sensor device 30 has almost the same configuration as the sensor device 10 shown in FIGS. 1 to 3, but has a different configuration in that a guide wire 31 is used instead of the catheter 11. ..

The guide wire 31 has a known structure, for example, is made of a polymer and a metal, and is selected to have an outer diameter of, for example, 350 μm. As shown in FIG. 9, the guide wire 31 is provided with a through hole 31a extending in the longitudinal direction for receiving the optical fiber 12 inside. The through hole 31a opens laterally near the tip of the guide wire 31 to define the window portion 31b as shown in FIG.

According to the sensor device 30 having such a configuration, by inserting the guide wire 31 of the sensor device 30 into the blood vessel of the patient, the guide wire 31 can be introduced into various parts of the body via the blood vessel. At that time, since the pressure near the tip of the guide wire 31 can be detected by the pressure sensor 13 via the window portion 31b, it is possible to accurately grasp the pathological condition by, for example, the pressure change before and after the narrowed portion of the blood vessel. ..

FIG. 11 shows a fourth embodiment of the sensor device according to the present invention. In FIG. 11, the sensor device 40 is a modification of the sensor device 30 shown in FIG. 8, and is provided with a plurality of pressure sensors 13 at substantially equal intervals from the vicinity of the tip of the guide wire 31, and each pressure is provided. The sensor is laterally exposed on the side surface of the guide wire 31 by a plurality of window portions 31b as shown in FIG. In this case, the guide wires 31 have a diameter of, for example, 0.46 mm, and the pressure sensors 13 are arranged at intervals of, for example, 25 mm. Each pressure sensor 13 is individually connected to an optical fiber (not shown) similar to the optical fiber 12.

According to the sensor device 40 having such a configuration, as shown in FIG. 12, by inserting the guide wire 31 of the sensor device 40 into the blood vessel 41 of the patient, the guide wire 31 is inserted into various parts of the body via the blood vessel 41. Can be introduced. At that time, since the pressure sensor 13 can detect each of the guide wires 31 at a plurality of locations in the longitudinal direction, for example, the pressure distribution before and after the stenosis portion 42 of the blood vessel is measured and the blood pressure changes before and after the stenosis portion 42. , Diagnosis of stenosis due to arteriosclerosis, evaluation of treatment by angioplasty and treatment may be stopped, so-called endpoint measurement can be easily performed, which is very effective clinically.

FIG. 13 shows a fifth embodiment of the sensor device according to the present invention. In FIG. 13, the sensor device 50 is a modification of the sensor device 30 shown in FIG. 8, and is attached to the tip surface of the optical fiber 12 embedded along the longitudinal direction in the guide wire 31 as a support member. In addition to the first pressure sensor 13 arranged facing the window portion 31b opened to the side of the guide wire 31, the tip surface of the guide wire 31 is also provided with the second pressure sensor 51. .. The second pressure sensor 51 is embedded so that the diaphragm (not shown) constituting the tip surface thereof protrudes from the tip surface of the guide wire 31 and is exposed and extends in the longitudinal direction of the guide wire 31. It is attached to the tip surface of the second optical fiber 52.

According to the sensor device 50 having such a configuration, when the guide wire 31 of the sensor device 50 is inserted into the blood vessel of the patient, the first pressure sensor 13 and the second pressure sensor 51 are used at two locations in the blood vessel. Blood pressure can be measured at the same time. Thereby, the blood flow velocity V in the blood vessel can be calculated based on the difference in pressure detected by the first pressure sensor 13 and the second pressure sensor 51. That is, when the intravascular pressure by the first pressure sensor 13 is P and the blood viscosity is ρ, the pressure due to the flow velocity acting on the tip surface of the guide wire 31 is the following equation P + (ρV).₂) / 2. Therefore, the blood flow velocity V in the blood vessel can be detected based on the difference in pressure detected by the first pressure sensor 13 and the second pressure sensor 51. In this way, the first pressure sensor 13 and the second pressure sensor 51 can be used as a flow velocity sensor. Of course, the support member may be a catheter instead of the guide wire 31.

FIG. 14 shows a sixth embodiment of the sensor device according to the present invention. In FIG. 14, the sensor device 60 is composed of an optical fiber 62 embedded along the longitudinal direction of the probe 61 of the endoscope and a pressure sensor 13 attached to the tip surface of the optical fiber 62. Here, the optical fiber 62 may be projected from the tip surface of the probe 61 of the endoscope, and the pressure sensor 13 may be attached to the tip surface exposed to the outside. In this case, as shown in FIG. 15, the pressure sensor 13 further includes a cover 63 made of an elastic material such as silicone rubber on the outer surface of the diaphragm 13a. As shown in FIG. 16, the cover 63 may wrap around the side surface of the pressure sensor 13 and extend to the periphery of the tip end portion of the optical fiber 62.

According to the sensor device 60 having such a configuration, when the probe 61 of the endoscope is inserted into the body of the patient, the cover 63 of the pressure sensor 13 attached to the tip of the probe 61 hits the inner wall of the esophagus, stomach, etc., for example. When they come into contact with each other, an external force is applied to the pressure sensor 13 via the cover 63, and the pressure sensor 13 detects the pressure. In this way, the pressure sensor 13 can be used as a force sensor or a tactile sensor.

In the above-described embodiment, the case where a catheter, a balloon catheter, a guide wire, an endoscope probe, or the like is used as the support member has been described, but the present invention is not limited to this, and a similar elongated hollow or solid support member is used. It is clear that the present invention can be applied.

In this way, according to the present invention, it is possible to reach a narrow portion that was conventionally difficult to insert due to the simple and compact configuration, and it is possible to perform precise measurement of a local part in the body. Further, it is possible to provide a sensor device that does not impose a burden on the patient or the like as much as possible.

<figref num="1">It is a schematic perspective view which shows the structure of the 1st Embodiment of the sensor device by this invention.</figref><figref num="2">It is a vertical sectional view of the sensor device of FIG.</figref><figref num="3">It is sectional drawing along the longitudinal direction of the sensor device of FIG.</figref><figref num="4">It is a partially enlarged sectional view which shows the structure of the pressure sensor used in the sensor device of FIG.</figref><figref num="5">It is (A) vertical sectional view and (B) horizontal sectional view which shows the use state of the sensor device of FIG.</figref><figref num="6">FIG. 6 is a schematic cross-sectional view showing the configuration of the second embodiment of the sensor device according to the present invention, in which (A) is the arrangement state of the pressure sensor inside the balloon, and (B) is the arrangement state of the pressure sensor in front of the balloon. (C) shows the placement state of the pressure sensor behind the balloon.</figref><figref num="7">The usage state of the sensor device of FIG. 6 is shown, (A) is a schematic cross-sectional view before balloon expansion, and (B) is a schematic cross-sectional view after balloon expansion.</figref><figref num="8">It is a schematic perspective view which shows the structure of the 3rd Embodiment of the sensor device by this invention.</figref><figref num="9">It is sectional drawing along the longitudinal direction of the sensor device of FIG.</figref><figref num="10">It is a top view of the sensor device of FIG.</figref><figref num="11">It is a schematic plan view which shows the structure of the 4th Embodiment of the sensor device by this invention.</figref><figref num="12">It is the schematic cross-sectional view which shows the use state of the sensor device of FIG.</figref><figref num="13">It is a schematic perspective view which shows the structure of the 5th Embodiment of the sensor device by this invention.</figref><figref num="14">It is a schematic plan view which shows the structure of the 6th Embodiment of the sensor device by this invention.</figref><figref num="15">FIG. 6 is a partially enlarged cross-sectional view of an example in which a pressure sensor is used as a force sensor or a tactile sensor in the sensor device of FIG.</figref><figref num="16">It is a partially enlarged sectional view which shows the modification of the force sensor or the tactile sensor of FIG.</figref>

Code description

10,20,30,40,50,60 Sensor device 11 Catheter 11a Through hole 11b Window 12 Optical fiber 12a Half mirror layer 13 Pressure sensor 13a Diaphragm 13b Reflective layer 13c Spacer 13d Mesa 14 Blood vessel 14a Blood vessel stenosis 21 Balloon catheter 21a Window 22 Balloon 23 Aortic wall 31 Guide wire 31a Through hole 31b Window 41 Blood vessel wall 42 Blood vessel stenosis 51 Second pressure sensor 52 Second optical fiber 61 Endoscope probe 62 Optical fiber 63 Cover