[go: up one dir, main page]

WO2013146259A1 - Dispositif médical optique et procédé de commande pour dispositif médical optique - Google Patents

Dispositif médical optique et procédé de commande pour dispositif médical optique Download PDF

Info

Publication number
WO2013146259A1
WO2013146259A1 PCT/JP2013/056972 JP2013056972W WO2013146259A1 WO 2013146259 A1 WO2013146259 A1 WO 2013146259A1 JP 2013056972 W JP2013056972 W JP 2013056972W WO 2013146259 A1 WO2013146259 A1 WO 2013146259A1
Authority
WO
WIPO (PCT)
Prior art keywords
optical
sheath
optical element
medical device
unit
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/JP2013/056972
Other languages
English (en)
Japanese (ja)
Inventor
圭一郎 山本
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Terumo Corp
Original Assignee
Terumo Corp
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Terumo Corp filed Critical Terumo Corp
Priority to JP2014507642A priority Critical patent/JP6103775B2/ja
Publication of WO2013146259A1 publication Critical patent/WO2013146259A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A61B5/0084—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for introduction into the body, e.g. by catheters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0062—Arrangements for scanning
    • A61B5/0066—Optical coherence imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6847—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive mounted on an invasive device
    • A61B5/6852—Catheters
    • A61B5/6855—Catheters with a distal curved tip

Definitions

  • the present invention relates to an optical medical device and an optical medical device control method, and more particularly to an optical medical device used by being inserted into a body lumen such as a blood vessel and a vascular vessel and an optical medical device control method.
  • diagnostic imaging has been performed by inserting a catheter having an imaging function into a blood vessel such as a coronary artery of the heart or a blood vessel such as a bile duct.
  • the diagnostic imaging apparatus examples include an optical coherence tomography (OCT) apparatus.
  • OCT optical coherence tomography
  • an optical element that irradiates light guided by an optical fiber into a living body lumen is movably disposed in the sheath, and the optical element is moved from the initial position on the distal end side of the sheath to the sheath.
  • the optical coherence tomographic image in the living body lumen is continuously acquired by the optical element while being moved backward toward the rear end position located on the base end side (hereinafter sometimes referred to as pullback) (for example, Patent Document 1).
  • OFDI optical frequency domain imaging method
  • the optical element In the optical coherence tomography apparatus, after acquiring an optical coherence tomographic image by pulling back from the initial position to the rear end position, the optical element is moved forward from the rear end position toward the initial position to return to the initial position (hereinafter referred to as the initial position). , Sometimes referred to as push forward).
  • the present invention has been made to solve the above-described problems, and provides an optical medical device and an optical medical device control method in which an optical element can surely return to an initial position in push-forwarding. Objective.
  • An optical fiber for guiding light and connected to a distal end side of the drive shaft that is inserted into the sheath, and irradiating light from the optical fiber into the living body lumen
  • An optical element for acquiring an optical coherence tomographic image, and an initial position connected to the proximal end side of the drive shaft and the optical element positioned on the distal end side of the sheath, and a rear end positioned on the proximal end side of the sheath
  • a drive unit that moves between the position and a position in which the optical element is moved backward from the initial position toward the rear end position by the drive unit,
  • a controller that continuously acquires coherence tomographic images, and when the controller moves the optical element forward from the rear end position toward the initial position by the driving unit,
  • the method for controlling an optical medical device that achieves the above object obtains an optical coherence tomographic image in the living body lumen by irradiating the living body lumen with light guided by an optical fiber.
  • An optical element is movably disposed in a bendable sheath, and the optical element is moved backward from an initial position located on the distal end side of the sheath toward a rear end position located on the proximal end side of the sheath by a driving unit.
  • a method for controlling an optical medical device that continuously acquires optical coherence tomographic images in the living body lumen by the optical element, wherein the optical element is moved from the rear end position by the driving unit to the initial position.
  • control unit detects the change in the light intensity distribution of the optical coherence tomographic image of the sheath due to the axial deformation of the optical fiber and controls the operation of the driving unit. be able to. For this reason, by appropriately controlling the operation of the drive unit, the load on the drive shaft is reduced, and the optical element can be returned to the initial position.
  • the operation of the drive unit is controlled by detecting the change in the light intensity distribution of the optical coherence tomographic image of the sheath due to the axial deformation of the optical fiber. be able to. For this reason, by appropriately controlling the operation of the drive unit, the load on the drive shaft is reduced, and the optical element can be returned to the initial position.
  • FIG. 1 is a schematic configuration diagram of an optical medical device according to an embodiment of the present invention. It is a longitudinal direction sectional view showing a joined portion of a sheath body part and a sheath tip member when the imaging core is pushed most into the sheath body part (advance limit position). It is longitudinal direction sectional drawing of a hub. It is the schematic which shows a catheter when an imaging core is pushed most into a sheath main-body part (advance limit position). It is the schematic which shows a catheter when an imaging core is most pulled out from the sheath main-body part (rear end position). It is longitudinal direction sectional drawing with a unit connector and a relay connector.
  • FIG. 9A is an image diagram of an optical coherent tomographic image of the sheath main body when the optical fiber is not contracted and deformed.
  • FIG. 9B is an optical diagram of the sheath main body when the optical fiber is contracted and deformed. It is an image figure of a tomographic image. It is a longitudinal direction sectional view when an imaging core passes the curved position of a sheath main-body part. It is the schematic which shows the speed of push forward of embodiment of this invention. It is a longitudinal direction sectional view of an imaging core when arranged in an initial position.
  • proximal end side the hand operating part side of the device
  • distal end side the side inserted into the living body lumen
  • FIG. 1 is a schematic configuration diagram of an optical medical device according to an embodiment of the present invention.
  • FIG. 2 is a longitudinal sectional view showing a joint portion between the sheath body and the sheath tip member.
  • an optical medical device 1 includes a bendable sheath 10 that is inserted into a body lumen such as a blood vessel and a vascular vessel, and a bendable sheath 10 that is mechanically inserted into the sheath 10.
  • a drive shaft 22 that transmits driving force, an optical fiber 41 that is provided in the drive shaft 22 and guides light, and a distal end side of the drive shaft 22 that is inserted into the sheath 10 are connected to the optical fiber 41. Is connected to the proximal end of the drive shaft 22 and the imaging core 21 is connected to the sheath 10.
  • a drive unit 60 that moves between an initial position located on the distal end side of the sheath 10 and a rear end position located on the proximal end side of the sheath 10, and a control unit 71 that controls the operation of the drive unit 60. That.
  • the control unit 71 controls the driving unit 60 to continuously move the imaging core 21 from the initial position toward the rear end position (pullback), and continuously generate the optical coherence tomographic image in the living body lumen by the imaging core 21. To get to.
  • the control unit 71 uses the imaging core 21 to light the optical coherence tomographic image of the sheath 10.
  • the brightness distribution is acquired, and the operation of the drive unit 60 is controlled when a change of the acquired light brightness distribution due to contraction deformation in the axial direction of the optical fiber 41 is detected. Details will be described below.
  • the sheath 10, the drive shaft 22, the optical fiber 41, and the imaging core 21 constitute an optical coherence tomography (OCT) catheter (hereinafter sometimes referred to as a catheter) 100.
  • OCT optical coherence tomography
  • the control unit 71 constitutes a control device 70.
  • the catheter 100 is a long and bendable sheath 10 that is inserted into a living body lumen, an image acquisition means 20 for acquiring an optical coherence tomographic image in the living body lumen, and a living body lumen. And an operation unit 30 that is connected to the proximal end side of the sheath 10 and is operated by a user without being inserted into the sheath 10.
  • the sheath 10 includes a sheath body 11 and a sheath tip member 12 and is configured by joining the sheath body 11 and the sheath tip member 12.
  • the sheath body 11 has a working lumen 11L in which the image acquisition means 20 is incorporated so as to be movable in the axial direction of the sheath 10.
  • the sheath tip member 12 has a guide wire lumen 12L through which the guide wire W is inserted.
  • the guide wire W is inserted into the living body lumen in advance, and the catheter 100 is guided to the affected part while passing the guide wire W through the sheath tip member 12.
  • an X-ray contrast marker 14 is provided in the vicinity of the distal end of the sheath distal end member 12 so that the distal end position of the catheter 100 can be confirmed under fluoroscopy when inserted into a living body lumen.
  • the tube wall of the sheath 10 is formed such that the proximal end side of the sheath distal end member 12 transmits an optical signal.
  • the catheter 100 according to the present embodiment is a catheter 100 that acquires an image by an optical signal using OCT, and an optical coherence tomographic image can be obtained by transmitting and receiving light through the tube wall of the sheath 10.
  • the image acquisition means 20 has an imaging core (optical element) 21 that houses a side-illuminated lens 212 for transmitting and receiving light toward a living body tissue in a housing 211, and the imaging core 21 is attached to the tip. And a drive shaft 22 for transmitting rotational power.
  • an imaging core optical element 21 that houses a side-illuminated lens 212 for transmitting and receiving light toward a living body tissue in a housing 211, and the imaging core 21 is attached to the tip.
  • a drive shaft 22 for transmitting rotational power.
  • the housing 211 is connected to the distal end side of the drive shaft 22, and the side irradiation type lens 212 is fixed to the distal end side of the optical fiber 41.
  • the fixing method is not particularly limited, and for example, it can be bonded with an adhesive.
  • the drive shaft 22 is flexible and has a characteristic capable of transmitting the mechanical driving force from the driving unit 60 transmitted through the optical connector 51 described later to the imaging core 21.
  • the imaging core 21 rotates and the affected part in the living body lumen can be observed 360 degrees.
  • the operation unit 30 is connected to the hub 31 on the proximal end side, the unit connector 33 connected to the hub 31 via the inner pipe 32, and the unit connector 33 via the outer pipe 34. And a relay connector 35 for connecting the sheath 10 and the operation unit 30.
  • FIG. 3 is a longitudinal sectional view of the hub 31. As shown in FIG. 3, the hub 31 includes a first outer housing 40 and a second outer housing 50.
  • the first outer housing 40 has a collar member 42 that defines the rotational axis of the drive shaft 22, and the drive shaft 22 and the optical fiber 41 are provided inside the second outer housing through the collar member 42. Connected to the optical connector 51.
  • the second outer housing 50 holds a part of the first outer housing 40 and rotatably holds an optical connector that transmits a mechanical driving force from the driving unit 60 to the drive shaft 22.
  • FIG. 4 is a schematic view showing the catheter 100 when the imaging core 21 is pushed most into the sheath body 11.
  • FIG. 5 is a schematic view showing the catheter 100 when the imaging core 21 is most pulled out from the sheath body 11.
  • the imaging core 21 when the imaging core 21 is pushed in most (hereinafter sometimes referred to as a forward limit position), that is, the imaging core 21 is in the sealing portion S on the distal end side of the sheath body 11.
  • a forward limit position when abutting (see FIG. 2), a gap G is generated between the front end side of the hub 31 and the rear end side of the unit connector 33. This is because the imaging core 21 is arranged on the distal end side of the sheath body 11 as much as possible.
  • the imaging core 21 is most pulled out from the sheath body 11, that is, when the inner tube 32 is most pulled out (hereinafter sometimes referred to as a rear end position), as shown in FIG.
  • the stopper 32A formed at the tip is hooked on the inner wall of the unit connector 33, and the portions other than the vicinity of the hooked tip are exposed.
  • the imaging core 21 is pulled back inside the sheath main body 11, and thus is positioned at a position facing the drive unit 60 by the amount of the inner tube 32 pulled out.
  • an optical coherence tomographic image in the living body lumen can be continuously acquired, and a three-dimensional image can be acquired.
  • FIG. 6 is a longitudinal sectional view of the unit connector 33 and the relay connector 35.
  • the unit connector 33 includes a unit connector main body 331, a sealing member 332, and a packing 333.
  • An outer tube 34 attached to the relay connector 35 is inserted into the unit connector body 331, and an inner tube 32 extending from the hub 31 is inserted into the outer tube 34.
  • the sealing member 332 holds the packing 333 in combination with the unit connector main body 331.
  • the inner pipe 32 extending from the hub 31 is formed with a stopper 32A at the tip, even when the hub 31 is most pulled, that is, when the inner pipe 32 is most pulled out from the outer pipe 34, the stopper 32A is The inner pipe 32 is not pulled out from the unit connector 33 by being caught on the inner wall of the connector main body 331.
  • the relay connector 35 holds the outer tube 34.
  • the proximal end of the sheath body 11 is connected to the inner surface of the relay connector 35, and a path for introducing the drive shaft 22 passing through the outer tube 34 into the sheath body 11 is formed.
  • the protective tube 7 is fixed to the inner wall of the outlet member 36 through which the drive shaft 22 of the relay connector 35 passes.
  • the protective tube 7 extends toward the inner tube 32 extending from the hub 31. Therefore, when the inner tube 32 is pushed into the outer tube 34, the protective tube 7 is pushed into the inner tube 32 in the direction opposite to the pushing direction. When the inner tube 32 is pushed into or pulled out from the outer tube 34, the protective tube 7 is also pushed into or pulled out from the inner tube 32 in the opposite direction. Therefore, even if the drive shaft 22 comes into contact with the inner tube 32 and friction occurs, and the force that bends to the drive shaft 22 is generated, the force that is deflected by the protective tube 7 can be suppressed, and bending or the like can be prevented.
  • the drive unit 60 includes an external drive source M such as a motor and a scanner device 61 including a detection unit 61 ⁇ / b> A that detects a pulse signal of the external drive source M and detects the position of the imaging core 21; An axial movement device 62 that holds the scanner device 61 and moves it in the axial direction by an external drive source M.
  • an external drive source M such as a motor
  • a scanner device 61 including a detection unit 61 ⁇ / b> A that detects a pulse signal of the external drive source M and detects the position of the imaging core 21;
  • An axial movement device 62 that holds the scanner device 61 and moves it in the axial direction by an external drive source M.
  • the scanner device 61 By connecting to the optical connector 51, the scanner device 61 transmits and receives light from the imaging core 21 and transmits a driving force for rotating the drive shaft 22 and the optical fiber 41.
  • the axial direction moving device 62 includes a scanner gripping portion 621 for gripping and fixing the scanner device 61, and a catheter support portion 622 that supports the sheath 10 so that it does not shift during movement.
  • the control device 70 includes a control unit 71 that controls the scanner device 61 and the axial movement device 62, and a display unit 72 that displays an image obtained by the light from the imaging core 21.
  • the optical coherence tomographic image is acquired by the optical medical device configured as described above by moving the imaging core 21 backward from the initial position toward the rear end position by the external drive source M in the scanner apparatus 61. This is done by rotating the imaging core 21 by an external drive source M in 61. Therefore, a cross-sectional image of 360 ° in the surrounding tissue body extending in the axial direction in the living body lumen can be obtained in a scanning manner up to an arbitrary position. Note that, at the forward limit position, the imaging core 21 abuts against the sealing portion S and a load is applied to the imaging core 21, so that the initial position is arranged at a position returned by, for example, 1 mm from the forward limit position to the base end side.
  • the reflected light from the living body lumen received by the imaging core 21 is transmitted to the control unit 71 via the optical fiber 41 and the optical connector 51, subjected to appropriate processing, and displayed on the display unit 72 as an optical coherence tomographic image.
  • the imaging core 21 After acquiring the optical coherence tomographic image, the imaging core 21 is returned from the rear end position to the initial position by the external drive source M in the scanner device 61 (push forward).
  • FIG. 7 is a flowchart showing the procedure of the control method of the optical medical device 1.
  • step S01 the control unit 71 controls the drive unit 60 to push the imaging core 21 forward from the rear end position toward the forward limit position at a speed of 10 mm / s, while the optical interference of the sheath main body 11 occurs.
  • the light intensity distribution of the tomographic image is acquired.
  • the drive unit 60 translates the drive shaft 22 along with the rotational motion, thereby acquiring the light intensity distribution in the radial direction of the optical coherence tomographic image as shown in FIG.
  • FIG. 8 is an image diagram showing the light luminance distribution of the sheath body 11 and the side irradiation type lens 212.
  • the horizontal axis indicates the radial distance
  • the vertical axis indicates the light luminance.
  • step S02 the rate of change a in the radial direction of the light luminance distribution of the sheath body 11 due to the contraction deformation in the axial direction of the optical fiber 41 is acquired.
  • the solid line indicates the light intensity distribution when the optical fiber 41 is not contracted and the broken line indicates the light intensity distribution when the optical fiber 41 is contracted and deformed.
  • the left side shows the side-illuminated lens 212
  • the center shows the inner wall 11A
  • the right side shows the outer wall 11B. From FIG. 8, the optical fiber is contracted and deformed so that the peak position of the light intensity is shifted to the left side, that is, the diameter is reduced.
  • the rate of change a is a light intensity peak position indicating the inner wall 11A when the optical fiber 41 is not contracted and deformed in FIG. 8, and a light peak indicating the inner wall 11A when the optical fiber 41 is contracted and deformed.
  • the position of intensity is ⁇ , it is obtained by ⁇ / ⁇ .
  • the rate of change of the peak position of the light intensity of the inner wall 11A is used as the rate of change a. May be.
  • the optical tomographic image as shown in FIG. 9 is displayed by the R ⁇ conversion by the control unit 71 based on the light luminance distribution obtained in FIG. 9A shows an optical coherence tomographic image of the sheath main body 11 and the imaging core 21 when the optical fiber 41 is not contracted and deformed, and FIG. 9B shows a sheath main body when the optical fiber 41 is contracted and deformed. 11 and optical core images of the imaging core 21 are shown.
  • the inner ring is an optical coherence tomographic image of the side-illuminated lens 212
  • the central ring is an optical coherence tomographic image of the inner wall 11 ⁇ / b> A of the sheath main body 11
  • the outer ring is the outer wall of the sheath main body 11.
  • 11B shows an optical coherence tomographic image of 11B, and an optical coherence tomographic image of the living body lumen L can be observed further outside.
  • 9A and 9B when the optical fiber 41 contracts and deforms in the axial direction, the diameters of the optical coherence tomographic images of the imaging core 21, the inner wall 11A, and the outer wall 11B are reduced.
  • the principle that the light intensity distribution changes when the optical fiber 41 contracts and deforms in the axial direction will be described. Since the optical coherence tomographic image is obtained by light interference between the measurement optical path and the reference optical path, when the axial contraction deformation occurs in the optical fiber 41, the distance of the measurement optical path changes, and the light luminance distribution Change. By using this principle to detect the contraction deformation of the optical fiber 41, it is possible to detect a catch on the sheath body 11 of the imaging core 21 or contact with the sealing portion S.
  • step S03 it is determined whether or not the position of the imaging core 21 detected by the detection unit 61A exists in a section that includes the rear end position and does not include the initial position (hereinafter may be referred to as a first section).
  • the first section is, for example, a case where the entire push-forward distance is 150 mm, and the range is from 150 mm to 10 mm when the forward limit position is the origin.
  • a section other than the first section and including the forward limit position and not including the rear end position (hereinafter sometimes referred to as a second section) is in the range of 10 mm to 0 mm.
  • step S04 the control unit sets the drive speed of the drive unit 60 to 10 mm / s. At this time, since the first push-forward speed is 10 mm / s, the driving speed of the driving unit 60 is maintained.
  • step S05 it is determined whether or not the change rate a acquired in step S02 exceeds a preset threshold value. When it is determined that the change rate a does not exceed the threshold (step S05: NO), the process returns to step S01.
  • step S05 the control unit sets the driving speed of the driving unit 60 to 1 mm / Slow down to s.
  • the cause of the change in the change rate a in this case is that the imaging core 21 is generated when the imaging core 21 passes through an extremely curved position of the sheath main body 11 to the sheath main body 11. This is contraction deformation in the axial direction of the optical fiber 41 due to the catch. 1 is different from the shape of the sheath 10 in FIG. 1, but this is a simplified description of the sheath 10 in FIG. 1 and is actually arranged along the living body lumen L. As a result, the sheath 10 is bent into various shapes.
  • step S06 After the control unit 71 sets the driving speed of the driving unit 60 to 1 mm / s in step S06, the light luminance distribution of the sheath main body 11 is acquired again in step S07, the rate of change a is acquired in step S08, and in step S05. Return to processing. Then, the process of step S06 is repeated until the change rate a does not exceed the threshold value. That is, the imaging core 21 is pushed forward at 1 mm / s. Then, after the imaging core 21 passes through the extremely curved position of the sheath main body 11, if the contraction deformation of the optical fiber 41 is lost, the change rate a does not exceed the threshold (step S05: NO), and again in step S01. Return to processing. When it is determined in step S03 that the imaging core 21 exists in the first section, in step S04, the control unit 71 sets the drive speed of the drive unit 60 to 10 mm / s.
  • step S09 the control unit 71 sets the drive speed of the drive unit 60 to 1 mm / s. To do.
  • step S10 it is determined whether or not the change rate a acquired in step S02 exceeds a preset threshold value.
  • the process returns to step S01.
  • the change rate a does not exceed the threshold value, the above process is repeated.
  • step S10 When it is determined that the rate of change a exceeds the threshold (step S10: YES), the imaging core 21 is returned to the initial position in step S11 as shown in FIG.
  • the cause of the change in the change rate a in this case is contraction deformation in the axial direction of the optical fiber 41 caused by the imaging core 21 coming into contact with the sealing portion S as shown in FIG.
  • step S12 After returning the imaging core 21 to the initial position in step S11, the operation of the drive unit 60 is stopped and terminated in step S12.
  • the control unit 71 performs light of the sheath main body 11 due to contraction deformation in the axial direction of the optical fiber 41.
  • a change in the light luminance distribution of the coherent tomographic image can be detected to control the operation of the drive unit 60. For this reason, by appropriately controlling the operation of the drive unit 60, the load on the drive shaft 22 is reduced, and the imaging core 21 can be returned to the initial position.
  • control unit 71 controls the operation of the driving unit 60 when the radial change rate a of the light luminance distribution exceeds a preset threshold value. For this reason, it is possible to automatically detect a change in the light luminance distribution of the sheath body 11 due to the contraction deformation of the optical fiber 41 in the axial direction. Therefore, it is possible to easily detect a change in the light luminance distribution of the sheath body 11 and control the operation of the drive unit 60, leading to an improvement in push forward workability.
  • the contraction deformation in the axial direction of the optical fiber 41 is contraction deformation caused by a load when the imaging core 21 passes through the curved position of the sheath main body 11, and the control unit 71 controls the drive unit 60.
  • the moving speed of the imaging core 21 is decreased. Therefore, a change in the light intensity distribution of the sheath main body 11 due to the contraction deformation in the axial direction of the optical fiber 41 that occurs when the imaging core 21 passes through the extremely curved position of the sheath main body 11 is detected, and the drive unit
  • the movement of the imaging core 21 can be stopped or the moving speed of the imaging core 21 can be reduced by controlling the operation of 60. Therefore, the load on the drive shaft 22 is reduced, the drive shaft 22 is prevented from being damaged, and push forward is maintained.
  • the controller 61A further detects whether or not the imaging core 21 is present in the first section, and the controller 71 detects that the imaging core 21 is present in the first section by the detector 61A.
  • the operation of the drive unit 60 is controlled when a change in the light luminance distribution is detected. For this reason, when the detection unit 61A determines that the imaging core 21 is present in the first section, the operation of the driving unit 60 is controlled to stop the movement of the imaging core 21 or reduce the moving speed of the imaging core 21. Can do. Therefore, more accurate push forward is possible.
  • the contraction deformation in the axial direction of the optical fiber 41 is contraction deformation caused by a load when the imaging core 21 abuts on the sealing portion S.
  • the control unit 71 controls the operation of the drive unit 60,
  • the imaging core 21 is stopped at an initial position set at a position separated from the forward limit position. For this reason, the change of the light intensity distribution of the sheath body 11 due to the contraction deformation in the axial direction of the optical fiber 41 caused by the imaging core 21 coming into contact with the sealing portion S is detected, and the operation of the drive unit 60 is controlled. Then, the imaging core 21 can be returned to the initial position set at a position separated from the forward limit position and stopped. Therefore, the load on the drive shaft 22 is reduced, and damage to the drive shaft 22 can be prevented.
  • the controller 61A further detects whether or not the imaging core 21 is present in the second section, the controller 71 detects that the imaging core 21 is present in the second section by the detector 61A, and When the change of the light luminance distribution is detected, the operation of the drive unit 60 is controlled. For this reason, when the detection unit 61A determines that the imaging core 21 is present in the second section, the operation of the drive unit 60 is controlled to stop the imaging core 21 at the initial position set at a position separated from the forward limit position. be able to. Therefore, more accurate push forward is possible.
  • the operation of the driving unit 60 is controlled when the rate of change a exceeds a preset threshold value, but the axial diameter of the optical coherence tomographic image exceeds the preset threshold value. Sometimes, the operation of the drive unit 60 may be controlled.
  • the detection unit 61A is used as means for detecting the position of the imaging core 21, but a position sensor provided at an appropriate place may be used.
  • the imaging core 21 is pushed forward at a speed of 1 mm / s, and the other positions P2 are pushed forward at a speed of 10 mm / s. It was done. However, these values can be arbitrarily set as appropriate.
  • the driving speed of the driving unit 60 is set to 1 mm / s.
  • the movement of the imaging core 21 may be stopped. At this time, it is inserted to a position where there is no resistance while being manually inserted and removed, and is automatically pushed forward again.
  • the driving speed of the driving unit 60 when the rate of change a exceeds a preset threshold, the driving speed of the driving unit 60 is decreased, but the driving speed of the driving unit 60 is decreased and repeatedly moved back and forth. You may let them.
  • Optical medical device 10 sheath, 11 sheath body, 21 Imaging core (optical element), 22 Drive shaft, 41 optical fiber, 60 drive unit, 61A detector, 71 control unit, 100 catheters, L biological lumen, S sealing part.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Pathology (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Endoscopes (AREA)
  • Investigating Or Analysing Materials By Optical Means (AREA)
PCT/JP2013/056972 2012-03-26 2013-03-13 Dispositif médical optique et procédé de commande pour dispositif médical optique Ceased WO2013146259A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
JP2014507642A JP6103775B2 (ja) 2012-03-26 2013-03-13 光学医療用デバイス及び光学医療用デバイスの制御方法

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2012070451 2012-03-26
JP2012-070451 2012-03-26

Publications (1)

Publication Number Publication Date
WO2013146259A1 true WO2013146259A1 (fr) 2013-10-03

Family

ID=49259523

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2013/056972 Ceased WO2013146259A1 (fr) 2012-03-26 2013-03-13 Dispositif médical optique et procédé de commande pour dispositif médical optique

Country Status (2)

Country Link
JP (1) JP6103775B2 (fr)
WO (1) WO2013146259A1 (fr)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2823767A4 (fr) * 2012-03-09 2015-10-28 Terumo Corp Cathéter
JP2017510309A (ja) * 2013-12-19 2017-04-13 ノバルティス アーゲー 前方走査光プローブ、円形走査パターン、オフセットファイバ
WO2019194313A1 (fr) * 2018-04-06 2019-10-10 京セラ株式会社 Système de cathéter

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2000262461A (ja) * 1999-02-04 2000-09-26 Univ Hospital Of Cleveland 光イメージング装置
JP2009240711A (ja) * 2008-03-31 2009-10-22 Terumo Corp 生体内挿入用プローブ装置
WO2010098014A1 (fr) * 2009-02-24 2010-09-02 テルモ株式会社 Dispositif de diagnostic par l'image et procédé de contrôle associé
JP2012013520A (ja) * 2010-06-30 2012-01-19 Fujifilm Corp 光断層画像化装置、及び、その光プローブ押付力推定方法

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2000262461A (ja) * 1999-02-04 2000-09-26 Univ Hospital Of Cleveland 光イメージング装置
JP2009240711A (ja) * 2008-03-31 2009-10-22 Terumo Corp 生体内挿入用プローブ装置
WO2010098014A1 (fr) * 2009-02-24 2010-09-02 テルモ株式会社 Dispositif de diagnostic par l'image et procédé de contrôle associé
JP2012013520A (ja) * 2010-06-30 2012-01-19 Fujifilm Corp 光断層画像化装置、及び、その光プローブ押付力推定方法

Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2823767A4 (fr) * 2012-03-09 2015-10-28 Terumo Corp Cathéter
US9872665B2 (en) 2012-03-09 2018-01-23 Terumo Kabushiki Kaisha Catheter
US10130337B2 (en) 2012-03-09 2018-11-20 Terumo Kabushiki Kaisha Catheter
US11076829B2 (en) 2012-03-09 2021-08-03 Terumo Kabushiki Kaisha Catheter
JP2017510309A (ja) * 2013-12-19 2017-04-13 ノバルティス アーゲー 前方走査光プローブ、円形走査パターン、オフセットファイバ
US10022187B2 (en) 2013-12-19 2018-07-17 Novartis Ag Forward scanning-optical probes, circular scan patterns, offset fibers
WO2019194313A1 (fr) * 2018-04-06 2019-10-10 京セラ株式会社 Système de cathéter
JPWO2019194313A1 (ja) * 2018-04-06 2021-04-01 京セラ株式会社 カテーテルシステム

Also Published As

Publication number Publication date
JP6103775B2 (ja) 2017-03-29
JPWO2013146259A1 (ja) 2015-12-10

Similar Documents

Publication Publication Date Title
JP5662846B2 (ja) カテーテル
US11259702B2 (en) Fiber optic imaging probe having cladding mode pullback trigger, and control method therefor
US8905936B2 (en) Catheter having a biasing member
JP2020039921A (ja) 延伸カテーテル本体ドライブシャフト支持を含む回転カテーテル
JP7460662B2 (ja) Ｏｃｔ管腔クリアランス用のレンジファインダ
JP5864182B2 (ja) モータ駆動装置及び画像診断装置
US9974526B2 (en) Ultrasonic endoscope biopsy system with treatment tool having various rigidity sections
JP2016059549A (ja) カテーテルおよびガイドワイヤ
JP6103775B2 (ja) 光学医療用デバイス及び光学医療用デバイスの制御方法
JP2011072680A (ja) 画像診断用カテーテル
JP6243769B2 (ja) 断層撮影装置およびその作動方法
JP2012217588A (ja) 医療用デバイス
JP6211874B2 (ja) 診断用カテーテル
EP2857057B1 (fr) Tube médical et procédé de production associé
JP5985131B1 (ja) 内視鏡用穿刺針及び生検システム
JP6430825B2 (ja) 医療用チューブのマーキング部形成方法、医療用チューブ、及び医療用デバイス
JP6786590B2 (ja) 画像診断カテーテル、補助デバイス及び補助デバイスの製造方法
WO2013146196A1 (fr) Dispositif médical
JP6612665B2 (ja) カテーテル及び画像診断装置
JP6400586B2 (ja) ガイドワイヤ
KR20240153119A (ko) 광음향-초음파 내시경
JP2014014591A (ja) 医療用デバイス

Legal Events

Date Code Title Description
121 Ep: the epo has been informed by wipo that ep was designated in this application

Ref document number: 13768767

Country of ref document: EP

Kind code of ref document: A1

ENP Entry into the national phase

Ref document number: 2014507642

Country of ref document: JP

Kind code of ref document: A

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 13768767

Country of ref document: EP

Kind code of ref document: A1