[go: up one dir, main page]

WO2015172322A1 - Dispositif et procédé de détection de la quantité d'écoulement sanguin - Google Patents

Dispositif et procédé de détection de la quantité d'écoulement sanguin Download PDF

Info

Publication number
WO2015172322A1
WO2015172322A1 PCT/CN2014/077418 CN2014077418W WO2015172322A1 WO 2015172322 A1 WO2015172322 A1 WO 2015172322A1 CN 2014077418 W CN2014077418 W CN 2014077418W WO 2015172322 A1 WO2015172322 A1 WO 2015172322A1
Authority
WO
WIPO (PCT)
Prior art keywords
light
signal
phase shift
module
shift signal
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/CN2014/077418
Other languages
English (en)
Chinese (zh)
Inventor
王益民
王辉
郭曙光
李鹏
何卫红
代祥松
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.)
Shenzhen Certainn Technology Co Ltd
Original Assignee
Shenzhen Certainn Technology Co Ltd
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 Shenzhen Certainn Technology Co Ltd filed Critical Shenzhen Certainn Technology Co Ltd
Priority to CN201480000246.7A priority Critical patent/CN104159505B/zh
Priority to PCT/CN2014/077418 priority patent/WO2015172322A1/fr
Priority to PCT/CN2015/071441 priority patent/WO2015172581A1/fr
Publication of WO2015172322A1 publication Critical patent/WO2015172322A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/02—Detecting, measuring or recording for evaluating the cardiovascular system, e.g. pulse, heart rate, blood pressure or blood flow
    • A61B5/026—Measuring blood flow

Definitions

  • the present invention relates to the field of optoelectronic technology, and in particular, to a blood flow measuring device and method.
  • retinal diseases are associated with abnormal blood flow to the eye, such as diabetic retinopathy, retinal vein occlusion, and age-related macular degeneration.
  • diabetic retinopathy retinopathy
  • retinal vein occlusion retinopathy
  • age-related macular degeneration retinopathy
  • measurement of retinal blood flow is important for clinical diagnosis, treatment, and research of retinal diseases.
  • OCT Optical Coherence Tomography
  • OCT is a non-invasive detection technique. It is widely used in the imaging of living structures in biological tissues. By measuring the scattered light associated with depth, OCT provides a highly resolved, highly sensitive tissue structure. At the same time, OCT technology can also detect the Doppler shift of scattered light to obtain motion information of fluids and samples, and is therefore suitable for measuring blood flow in the retina.
  • the frequency shift detected by the single-beam Doppler OCT is only related to the blood flow velocity in the direction of the probe beam, and the blood flow information perpendicular to the direction of the probe light cannot be directly obtained from the Doppler shift, and the intravascular can not be obtained. The actual flow rate.
  • (1) through three-dimensional scanning of the retina, obtain the direction of the blood vessels in the retina in space, thereby determining the Doppler angle of the probe light, and then using the Doppler angle to calculate the actual flow velocity.
  • this method is less accurate because the blood vessels of the retina and the probe beam are close to vertical.
  • the space vector of the blood vessel to be tested is determined, and then the Doppler angle is calculated to obtain the actual flow velocity.
  • the measurement results of this method are affected by eye movements, and it can only measure blood vessels around the optic disc and cannot measure blood flow in other areas of the retina.
  • flow information can be obtained by calculating the Doppler signal of the cross-section of the blood vessel, but this measurement method is only applicable to large vessels that are steep toward the optic disc. Blood flow to other areas of the retina cannot be detected.
  • the OCT probe light is split into two beams by a glass plate.
  • the two beams are concentrated in the fluid to form a double beam.
  • the two-angle illumination method can be obtained by analyzing the Doppler shift detected by the two beams.
  • - - The actual fluid velocity into the pipe. This method is not suitable for frequency domain OCT systems due to the delay of the two paths of light.
  • a dual beam OCT system with polarized beam splitting can be used to measure the flow rate and flow rate in the retinal blood vessels, or a DOVE prism can be synchronized with the OCT scanning mechanism to achieve a circular scan of the dual beam on the retina.
  • an object of the present invention is to provide a blood flow measuring device which realizes single beam, double angle detection and scanning through a rotatable mirror to obtain blood flow of blood vessels in the eye, and the device has a simple structure. , Easy adjustment, high measurement accuracy, etc., to meet the requirements of use.
  • the present invention also provides a blood flow measuring method based on the above blood flow measuring device.
  • a blood flow measuring device for measuring blood flow of a blood vessel in an eye, comprising a light source, a first beam splitting module, a reference arm module, a sample arm module, and a detecting module, wherein
  • the sample arm module includes a rotatable mirror,
  • the light source emits light and transmits the light to the first beam splitting module, and the first beam splitting module supplies the received light to the reference arm module and the sample arm module, respectively, and the reference arm module receives The received light is transmitted back to the first beam splitting module to form reference light;
  • the signal light is transmitted back to the first beam splitting module and interferes with the reference light in the first beam splitting module to generate interference light, and the detecting module receives the interference light.
  • the sample arm module further includes a motor, the motor has a rotating shaft, and the rotatable mirror is fixed on the rotating shaft, and the rotating mirror drives the rotatable mirror to rotate correspondingly.
  • the sample arm module further includes a scanning unit, a dichroic mirror and an ophthalmoscope, the scanning unit includes a first scanning element and a second scanning element, and the first scanning element receives the rotatable mirror - reflecting light and reflecting to the second scanning element, the second scanning element reflecting the received light to the dichroic mirror, the dichroic mirror reflecting the received light to the ophthalmoscope
  • the ophthalmoscope concentrates light onto the eye.
  • the sample arm module further includes a collimating lens disposed between the rotatable mirror and the first scanning element, and the relay lens is disposed on the second scan Between the component and the dichroic mirror.
  • the sample arm module further includes a preview module, the preview module includes an imaging lens and a camera, and light emitted by the illumination source is irradiated to the eye, and reflection occurs in the eye, and the reflected light transmits the reflected light
  • the ophthalmoscope, the dichroic mirror, and the imaging mirror are then passed to the camera to be photographed by the camera.
  • the device further comprises a computer, the computer receiving the signal processed by the detecting module, and controlling the rotation of the motor, the first scanning element and the second scanning element.
  • the present invention also provides a blood flow measuring method, characterized in that it comprises at least the following steps: when the rotatable mirror is at a first rotation angle, transmitting probe light to the blood vessel and generating a first signal light, The first signal light after the interference is processed to obtain a first phase shift signal; when the rotatable mirror is at the second rotation angle, the probe light is transmitted to the blood vessel and the second signal light is generated, after the interference The second signal light is processed to obtain a second phase shift signal; and the blood flow of the blood vessel is calculated according to the first phase shift signal and the second phase shift signal.
  • the first signal light after the interference is obtained by interfering with the first signal light when receiving the first signal light;
  • the interfering second signal light is obtained by interfering with the second signal light when the second signal light is received.
  • the method further includes:
  • the method further includes: A pair of said second phase shift signals are corrected.
  • the correcting the second phase shift signal includes:
  • the second phase shift signal is corrected using an interpolation calculation.
  • the method before calculating the blood flow of the blood vessel according to the first phase shift signal and the second phase shift signal, the method further includes:
  • the blood flow measuring device and method provided by the present invention controls the rotation of the rotatable mirror by a motor such that the rotatable mirror is at a first rotation angle and obtains a first phase shift signal, or the rotatable mirror is made At a second rotation angle and obtaining a second phase shift signal, the flow rate of the blood is obtained by processing the first phase shift signal and the second phase shift signal.
  • the blood flow measuring device provided by the invention has the advantages of simple structure, convenient operation, high precision of measurement results, and the like when measuring blood flow.
  • FIG. 1 is a schematic structural view of a blood flow measuring device according to an embodiment of the present invention.
  • FIG. 2 is a schematic structural diagram of another reference arm module according to an embodiment of the present invention.
  • Figure 3 is a schematic view showing the structure of the sample arm module shown in Figure 1.
  • Fig. 4 is a view showing the positional relationship between the first direction vector and the second direction vector and the blood vessel.
  • Figure 5 is a schematic illustration of the scanning trajectory of the probe light within the blood vessel.
  • Fig. 6 is a schematic diagram showing the principle of realizing the scanning trajectory shown in Fig. 4.
  • Fig. 7 is a schematic view showing the scanning of the angle between the axial direction of the blood vessel and the X direction.
  • FIG. 8 is a schematic flow chart of a blood flow measurement method according to a first embodiment of the present invention.
  • FIG. 9 is a schematic flow chart of a blood flow measurement method according to a second embodiment of the present invention.
  • Figure 10 is a graph showing changes in the first phase shift signal and the second phase shift signal over time.
  • an embodiment of the present invention provides a blood flow measuring device for measuring blood flow of a blood vessel in an eye 800, which may be the eye of a human eye or other animal.
  • the blood flow measuring device includes a light source 100, a first beam splitting module 200, a reference arm module 300, a sample arm module 500, a detecting module 600, and a computer 700, and the light source 100 emits light and transmits the light to the first beam splitting module. 200.
  • the first beam splitting module 200 divides the received light into two beams and provides the reference arm module 300 and the sample arm module 500, respectively. One of the light is transmitted to the reference arm module 300, which transmits the received light back into the beam splitter module 200 to form reference light, and the other beam passes through the sample arm module 500.
  • the signal light After being incident into the eye 800, the signal light is scattered by the blood vessel in the eye 800 and returned to the first beam splitting module 200, and the signal light interferes with the reference light to generate interference light, the detecting Module 600 receives and collects the interference light and transmits the signal to computer 700, which processes the signal.
  • the light source 100 may be a super luminescent diode that emits near-infrared detection light, and the probe light is transmitted to the first beam splitting module 200, and the first beam splitting module 200 may It is a 2 x 2 fiber splitter that splits the received probe light into two beams and supplies them to the reference arm module 300 and the sample arm module 500, respectively.
  • the reference arm module 300 includes a reference mirror 303, wherein the reference mirror 303 can be a planar mirror, and the probe light provided by the first beam splitting module 200 passes the reference The mirror 303 is vertically reflected and returned to the first beam splitting module 200 to form reference light.
  • FIG. 2 is another reference arm module 900 according to an embodiment of the present invention.
  • the reference arm module 900 includes a second beam splitting module 901, and the second beam splitting module 901 can be 1 X.
  • the 2 beam splitter has an opening at one end and two openings at the other end and the two openings are connected by an optical path of the optical fiber.
  • the probe light provided by the first beam splitting module 200 is incident from the one end with one opening into the second beam splitting module 900, and then exits from the two openings at the other end respectively, and propagates in the optical fiber and returns to the respective
  • the second beam splitting module 900 finally exits from an end with an opening and returns to the first beam splitting module 900 to form reference light.
  • the reference arm module may have other structural design and placement manners, such as the second beam splitting module 901 may be disposed on the first beam splitting module 200 and Between the detection modules 600, the light provided by the first beam splitting module 200 to the reference arm module 901 is transmitted through the optical fiber to the second beam splitting module 901 to form reference light (from one end with two openings) One opening is incident). The signal light reflected back by the sample arm module 500 is incident into the second beam splitting module 901 (incident from another one of the ends with two openings) and interferes with the reference light to form interference light, The interference light is transmitted from the end with an opening and then transmitted to the detecting module 600.
  • the reference arm module has other designs, which are not limited herein.
  • the blood flow measuring device further includes a first lens 400, and the first lens 400 is disposed in the first beam splitting module 200 and the sample arm module 500.
  • the probe light provided by the first beam splitting module 200 is transmitted to the sample arm module 500 after being transmitted through the first lens 400.
  • the sample arm module 500 includes a motor 502, a rotatable mirror 503, a scanning unit, a dichroic mirror 508, and an ophthalmoscope 509.
  • the motor 502 has a rotating shaft, the rotatable mirror 503 is fixed on the rotating shaft, and the motor 502 rotates to rotate the rotating shaft, so that the rotatable mirror 503 rotates with the motor 502. Rotating to inject the probe light provided by the first beam splitting module 200 into the eye 800 at different angles.
  • the scanning unit includes a first scanning component 505 and a second scanning component 506, wherein the first scanning component 505 can be an X-direction scanning component.
  • the second scanning element 506 can be a Y-direction scanning element.
  • the motor 502 rotates and drives the rotatable mirror 503 to rotate when the rotatable mirror 503 is at a first rotation angle M l 5 In this case the rotatable mirror 503 reflecting the first partial optical beam provided by the module 200 to the first scanning element 505, after passing through the first scanning element 505 to the second reflector Scanning element 506.
  • the second scanning element 506 reflects the probe light incident on the surface thereof to the dichroic mirror 508, and the dichroic mirror 508 can be a dichroic mirror having a high reflectivity to the probe light, the two-color
  • the mirror 508 reflects the probe light to the ophthalmoscope 509, and the eyepiece 509 converges to the blood vessel in the eye 800.
  • the blood vessel B scatters the probe light to generate a first signal light.
  • the reference light interferes to generate first interference light, and the detection module 600 receives the first interference light and is collected and processed by the computer 700 to obtain a first phase shift signal.
  • the incident path of the probe light may refer to the path 1 indicated by the solid line in FIG. 3, and the probe light is incident into the eye 800 via the path 1.
  • the first direction vector can be represented by Si (as shown in Figure 4).
  • the rotatable mirror 503 When the motor 502 is rotated through a predetermined angle, such as 180 degrees, the rotatable mirror 503 is at a second rotational angle M 2 . At this time, the rotatable mirror 503 reflects the light provided by the first beam splitting module 200 to the first scanning element 505, is reflected by the first scanning element 505, and is transmitted to the second scanning element. 506.
  • the second scanning element 506 reflects the probe light incident on the surface thereof to the dichroic mirror 508, which may be a dichroic mirror having a high reflectivity to the probe light, the two-color
  • the mirror 508 reflects the probe light to the ophthalmoscope 509, and is concentrated by the ophthalmoscope 509 to the blood vessel B in the eye 800.
  • the blood vessel B scatters the probe light to generate a second signal light, and the second signal light returns to the first beam splitting module 200 in a direction opposite to the incident light and interferes with the reference light to generate The second interference light, the detection module 600 receives the second interference light and is collected by the computer 700 to obtain a second phase shift signal.
  • the incident path of the probe light may refer to the path 2 indicated by a broken line in FIG. 3 , and the probe light is incident into the eye 800 via the path 2 .
  • the second direction vector can be represented by S 2 (as shown in FIG. 4).
  • the sample arm module 500 further includes a second lens 501 disposed between the first lens 400 and the rotatable mirror 503, and the second lens 501 The light provided by the first lens 400 converges to the surface of the rotatable lens 503.
  • the sample arm module 500 further includes a collimating lens 504 and a relay lens 507.
  • the collimating lens 504 is disposed between the rotatable mirror 503 and the first scanning element 505, and the detecting light reflected by the rotatable mirror 503 is transmitted through the collimating lens 504 to reach the First scanning element 505.
  • the relay lens 507 is disposed between the second scanning element 506 and the dichroic mirror 508, and the probe light reflected by the second scanning element 506 is transmitted through the relay lens 507 to reach the dichroic mirror 508.
  • the sample arm module 500 further includes a preview module, and the preview module includes an imaging lens 510 and a camera 511, and light emitted by an illumination source (not shown) is irradiated to the eye 800, and Reflection occurs in the eye 800, the reflected light is transmitted through the ophthalmoscope 509 to the dichroic mirror 508, and the dichroic mirror 508 has a high transmittance to the light emitted by the illumination source, and the reflected light sequentially transmits the After the dichroic mirror 508 and the imaging lens 510 arrive at the camera 511, the image captured by the camera 511 is displayed on the computer display screen for the operator to understand the eye. Information about 800 for further operation.
  • the first scanning element 505 and the second scanning element 506 may be galvanometers, and the first scanning element 505 has an effect of performing X-direction scanning on the probe light.
  • the second scanning element 506 has a function of scanning the detection beam in the Y direction. Specifically, as shown in FIG.
  • the first direction vector Si and the second direction vector S 2 form an XZ plane
  • the scanning unit rotates and Detecting the detection light whose incident direction is the first direction vector Si
  • the scanning unit rotates and drives the detection direction of the second direction vector S 2
  • the light is scanned to ensure that the probe light can detect the blood vessel B.
  • the computer 700 according to the received signal a first mobile phase, the second phase and the movement signal related parameters (e.g., wavelength of the probe light, the refractive index of the blood, a first direction and the second direction vector Si sandwiched between the two vector S The angle between the axial direction of the blood vessel and the blood vessel and the X direction, etc.), the average blood flow rate of the blood vessel B is calculated.
  • the movement signal related parameters e.g., wavelength of the probe light, the refractive index of the blood, a first direction and the second direction vector Si sandwiched between the two vector S
  • the average blood flow rate of the blood vessel B is calculated.
  • the scanning unit can drive the detection by the cooperation of the first scanning element 505 and the second scanning unit 506.
  • the light beam realizes various scanning modes such as X-direction scanning, Y-direction scanning, or oblique line scanning, so that the detection light adjusts the scanning direction according to the actual direction of the blood vessel B.
  • the blood flow measuring device can also implement a circular sweep by the cooperation of the first scanning element 505, the second scanning element 506 and the motor 502. - - Trace to quickly obtain blood flow from all blood vessels throughout the eye 800.
  • the computer 700 controls the synchronous rotation of the motor 502 with the first scanning element 505 and the second scanning element 506, thereby
  • the detection ray is circularly scanned around the optic disc region on a circumference C.
  • Figure 6 depicts how such scanning can be accomplished: First, the first scanning element 505, the second scanning element 506 controls the detection beam onto the circumference.
  • the motor 502 rotates 360 degrees, and the probe beam will move circumferentially around the tapered surface Co.
  • the motor 502 rotates synchronously with the first scanning element 505 and the second scanning element 506, the detecting beam will complete a circular motion along the direction of the space vector shown by the solid line (the inner ring of the circle shown in FIG. 6).
  • the first phase shift signal corresponding to each blood vessel can be obtained.
  • the motor 502 quickly switches a phase ⁇ (i.e., turns 180 degrees), at which point the probe beam switches to the direction indicated by the dashed line (outer ring shown in Figure 6).
  • the first scanning element 505 and the second scanning element 506 are synchronously moved with the motor 502 to drive the detecting beam to perform a circular motion along the direction of the space vector indicated by the broken line, thereby obtaining a second phase moving signal corresponding to each blood vessel.
  • the scan is performed for a predetermined time (e.g., 2 seconds), and the computer 700 can collect a series of phase shift signals.
  • the scanning beam is scanned for a fast multi-ring to obtain a circular three-dimensional image. As shown in Fig. 7, the angle ⁇ between the axial direction of all the blood vessels and the X direction can be determined.
  • the computer 700 obtains the total blood flow rate in the eye 800 by calculating the average blood flow rate of each blood vessel and superimposing it.
  • the blood flow measuring device controls the rotation of the rotatable mirror 503 by the motor 502 such that the rotatable mirror 503 is at the first rotation angle Mi and obtains a first phase shift signal, or The rotatable mirror 503 is at a second rotation angle M 2 and obtains a second phase shift signal, and the actual flow rate of the blood is obtained by processing the first phase shift signal and the second phase shift signal and thereby obtaining blood. flow.
  • the blood flow measuring device provided by the embodiment of the invention has the advantages of simple structure, convenient operation and high precision of measurement results when measuring blood flow.
  • an embodiment of the present invention provides a blood flow measurement method, which includes at least the following steps.
  • the computer 700 can control the rotation of the motor 502 to cause the rotatable mirror 503 fixed on the motor 502 to be at the first rotation angle M l at this time, the light source
  • the probe light emitted by 100 will propagate along the solid path 1 as shown in FIG. 3 to the vasospasm of the eye 800.
  • the vasospasm scatters the probe light to generate a first signal light, and the first signal light is transmitted back to the first beam splitting module 200 and interferes with the reference light, and the interfered first signal light is detected by the detecting Module 600 receives and communicates to computer 700, which processes the first signal light after interference to generate a first phase shift signal.
  • the computer 700 can switch the rotatable mirror 503 fixed on the motor 502 from the first rotation angle to the second rotation angle by controlling the rotation of the motor 502. M 2 , at this time, the probe light emitted by the light source 100 will propagate to the blood vessel B of the eye 800 along the dashed path 2 as shown in FIG. 3 .
  • the blood vessel B scatters the probe light to generate a second signal light, and the second signal light is transmitted back to the first beam splitting module 200 and interferes with the reference light, and the interfered second signal light is detected by the detecting Module 600 receives and communicates to computer 700, which processes the interfered second signal light to generate a second phase shift signal.
  • the computer 700 calculates the blood flow of the blood vessel B based on the received first phase shift signal and the second phase shift signal.
  • the blood flow measuring method controls the rotation angle of the rotatable mirror 503 to respectively generate a first phase shift signal and a second phase shift signal, and passes the first phase shift signal and the second phase.
  • the moving signal calculates the blood flow of the blood vessel B, and the measuring method has the advantages of small error in measurement result and simple operation process.
  • a second embodiment of the present invention provides a blood flow measuring method, which includes at least the following steps.
  • the computer 700 can control the rotation of the motor 502 to cause the rotatable mirror 503 fixed on the motor 502 to be at the first rotation angle M l at this time, the light source
  • the probe light emitted by 100 will propagate along the solid line path 1 as shown in FIG. 3 to the blood vessel B of the eye 800, and the blood vessel B scatters the probe light to generate a first signal light, which is transmitted back to the first signal light.
  • the first beam splitting module 200 interferes with the reference light, and the interfered first signal light is received by the detecting module 600 and transmitted to the computer 700, and the computer 700 processes the interfered first signal light. , generating the first phase shift signal
  • the computer 700 controls the rotatable mirror 503 fixed on the motor 502 by controlling the rotation of the motor 502 (eg, the motor 502 is rotated through 180 degrees).
  • the first rotational angle is switched to the second rotational angle M 2 , at which time the probe light emitted by the light source 100 will propagate along the dashed path 2 as shown in FIG.
  • the blood vessel B scattering Generating a second signal light after detecting the light
  • the second signal light is transmitted back to the first beam splitting module 200 and interferes with the reference light
  • the interfered second signal light is received by the detecting module 600 and transmitted
  • the computer 700 processes the second signal light after the interference to generate a second phase shift signal ⁇ 2 .
  • the first phase shift signal 1 and the second phase shift signal ⁇ 2 are not coincident with each other, and the blood flow in the blood vessel is pulsating, blood at different times The flow rate is different, so the computer 700 needs to correct the first phase shift signal 1, and the correction process includes the following steps:
  • the relationship between the first phase shift signal 1 and the second phase shift signal ⁇ 2 over time is obtained by scanning by the scanning unit.
  • the scanning unit drives the first plane and the second direction vector S 2 formed by the beam to the first direction vector Si and the x-axis.
  • the formed second plane is alternately scanned for a predetermined time, such as 2 seconds, to obtain a time-dependent phase shift signal profile (as shown in Figure 10).
  • the computer 700 collects the first phase shift signal ⁇ white at different time points on the first plane as the rotatable
  • the second phase shift signal ⁇ 2 measured by the computer 700 at different time points on the second plane.
  • the scanning unit can drive the detection by the cooperation of the first scanning element 505 and the second scanning unit 506.
  • the light beam realizes various scanning modes such as X-direction scanning, ⁇ direction scanning or oblique line scanning, and the above-mentioned scanning of the first plane and the second plane is only one possible scanning mode of the present invention, and in other embodiments of the present invention,
  • the scanning unit can also drive the light beam to scan along other planes of the space according to the direction of the vasospasm.
  • the second phase shift signal ⁇ 2 is corrected by interpolation calculation.
  • O al mobile phase is a first signal obtained by scanning moment t ⁇ , O b2 for the second mobile phase timing signal b obtained by scanning 10 t shown in FIG.
  • the processor may also fit the fitting equation of the phase shift signal and time by other fitting algorithms, and then correct the second phase shift signal ⁇ 2 .
  • the first phase shift signal and the second phase shift signal at the same time are obtained, and are not limited to the interpolation algorithm provided by the embodiment of the present invention.
  • the processor may further perform the interpolation calculation on the first phase shift signal, such as by performing interpolation calculation on the second phase shift signal measured on the second plane.
  • T a k multiplied with the time to a first mobile phase signal O al, t thus obtained to a first mobile phase timing signal ⁇ b ⁇ ,, D bl kO al. - -
  • the processor when calculating the flow rate of the blood vessel B, the processor first needs to obtain an angle ⁇ between the axial direction of the blood vessel B to be tested and the X direction.
  • the mirror when the mirror is at the first rotation angle, when the probe enters the first direction vector Si of the eye 800 and the mirror is at the second rotation angle M 2 , the light enters the second direction vector of the eye S 2 constitutes an XZ plane which is parallel to the X-axis of the XZ plane.
  • the angle ⁇ is as shown in Fig. 4, and the angle ⁇ can be obtained only by obtaining a spatial distribution of the desired vasospasm.
  • the first phase shift signal O al and the probe light measured by the probe light at the first rotation angle of the rotatable mirror 503 are at the second rotation angle M of the rotatable mirror 503. 2 measured second phase shift signal ⁇ ⁇ , that is, the flow rate of the vasospasm at time t a can be obtained ⁇
  • ⁇ is the time interval between two adjacent scans, which is the angle between the first direction vector Si and the second direction vector S 2 (see Figure 4). Shown), ⁇ is the angle between the axial direction of the blood vessel and the X direction. Considering the pulsation of blood flow, the flow velocity of blood in the blood vessel at any time can be expressed as:
  • V(y, z,t) v A (y, z)P(t)
  • the processor obtains the average flow of blood in the blood vessel B by integrating the space and time:
  • T is the pulsation period of the blood flow
  • P(t) is the blood flow pulsation function in the vasospasm measured as shown in FIG.
  • the blood flow measurement method provided by the embodiment of the present invention can also quickly measure the blood flow of all blood vessels in the eye 800, that is, the total blood flow of the eye 800.
  • the motor 502 cooperates with the first scanning element 505 and the second scanning element 506 to effect a circular scan of the eye 800.
  • the computer 700 controls the synchronous rotation of the motor 502 with the first scanning element 505 and the second scanning element 506. Thereby the detection light is circularly scanned around the optic disc region on a circumference C.
  • Figure 6 depicts how such scanning is achieved: First, the first scanning element 505 and the second scanning element 506 control the detection beam to At point S on the circumference, if the first scanning element 505 and the second scanning element 506 remain stationary and the motor 502 rotates 360 degrees, the probe beam will move circumferentially around the tapered surface Co. When the motor 502 rotates synchronously with the first scanning element 505 and the second scanning element 506, the probe beam will complete a space vector direction along the solid line (the inner ring of the circle shown in FIG. 6). The circular motion, thus obtaining the first phase shift signal corresponding to each blood vessel.
  • the motor 502 quickly switches a phase ⁇ , at which point the beam will switch to the direction indicated by the dashed line (outer ring shown in Figure 6). Then, the first scanning element 505 and the second scanning element 506 move synchronously with the motor 502 to drive the light beam to move in a circular motion along the direction of the space vector indicated by the broken line, so as to obtain a second phase shift corresponding to each blood vessel.
  • the signal scanned for a predetermined time (e.g., 2 seconds), the computer 700 can collect a series of phase shift signals. After the above scanning is completed, the scanning beam is scanned for a fast multi-ring to obtain a circular three-dimensional image. As shown in Fig.
  • the angle ⁇ between the axial direction of all the blood vessels and the X direction can be determined.
  • the computer 700 obtains the total blood flow rate in the eye 800 by calculating the average blood flow rate of each blood vessel and superimposing it.
  • the blood flow measurement method controls the rotation angle of the rotatable mirror 503 to generate a first phase shift signal and a second phase shift signal, respectively, and After the phase shift signal or the second phase shift signal is corrected, the blood flow direction, the pulsation and the period are obtained by scanning, and the blood flow rate of the blood vessel fistula and the total blood flow rate in the eye 800 are obtained by integral calculation.
  • the measuring method Easy to operate, less error in measurement results, etc. - - Point.

Landscapes

  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • General Health & Medical Sciences (AREA)
  • Physics & Mathematics (AREA)
  • Veterinary Medicine (AREA)
  • Biophysics (AREA)
  • Public Health (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Animal Behavior & Ethology (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Hematology (AREA)
  • Physiology (AREA)
  • Pathology (AREA)
  • Cardiology (AREA)
  • Ophthalmology & Optometry (AREA)
  • Eye Examination Apparatus (AREA)
  • Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
  • Investigating Or Analysing Materials By Optical Means (AREA)

Abstract

L'invention concerne un dispositif et procédé de détection de la quantité d'écoulement sanguin, lequel dispositif de détection de la quantité d'écoulement sanguin comprend une source de lumière (100), un premier module faisceau (200), un module bras de référence (300), un module bras échantillon (500) et un module sonde (600), le module bras échantillon (500) comprenant une lentille réfléchissante rotative (503), la source de lumière (100) émettant de la lumière et la transmettant vers le premier module faisceau (200), lequel achemine respectivement le rayonnement reçu vers le module bras de référence (300) et le module bras échantillon (500). Le module bras de référence (300) renvoie le rayonnement reçu vers le premier module faisceau (200) pour former une lumière de référence. Lorsque ladite lentille réfléchissante rotative (503) forme un premier angle de rotation (M1), la lumière provenant du premier module faisceau (200) dirigée vers les yeux forme un premier signal lumineux. Lorsque ladite lentille réfléchissante rotative (503) forme un second angle de rotation (M2), la lumière provenant du premier module faisceau (200) dirigée vers les yeux forme un second signal lumineux. Les premier et second signaux lumineux sont renvoyés vers le premier module faisceau (200) et là ils forment respectivement avec une interférence de référence des première et seconde interférences lumineuses envoyées vers le module sonde (600).
PCT/CN2014/077418 2014-05-14 2014-05-14 Dispositif et procédé de détection de la quantité d'écoulement sanguin Ceased WO2015172322A1 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
CN201480000246.7A CN104159505B (zh) 2014-05-14 2014-05-14 血液流量测量装置及方法
PCT/CN2014/077418 WO2015172322A1 (fr) 2014-05-14 2014-05-14 Dispositif et procédé de détection de la quantité d'écoulement sanguin
PCT/CN2015/071441 WO2015172581A1 (fr) 2014-05-14 2015-01-23 Appareil et procédé de mesure de flux sanguin

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
PCT/CN2014/077418 WO2015172322A1 (fr) 2014-05-14 2014-05-14 Dispositif et procédé de détection de la quantité d'écoulement sanguin

Publications (1)

Publication Number Publication Date
WO2015172322A1 true WO2015172322A1 (fr) 2015-11-19

Family

ID=51884814

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/CN2014/077418 Ceased WO2015172322A1 (fr) 2014-05-14 2014-05-14 Dispositif et procédé de détection de la quantité d'écoulement sanguin

Country Status (2)

Country Link
CN (1) CN104159505B (fr)
WO (1) WO2015172322A1 (fr)

Cited By (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3305187A4 (fr) * 2015-05-27 2019-02-13 Shenzhen Certainn Technology Co., Ltd. Appareil et procédé permettant de mesurer le débit sanguin dans un vaisseau sanguin

Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2015172581A1 (fr) * 2014-05-14 2015-11-19 深圳市斯尔顿科技有限公司 Appareil et procédé de mesure de flux sanguin
CN105286779B (zh) * 2015-10-30 2017-06-30 温州医科大学 一种在体视网膜血流动力学的成像与绝对流速测量方法
CN109223044B (zh) * 2018-07-12 2021-08-24 郑州轻工业学院 一种光学相干层析成像系统的多普勒流速检测方法
CN109124686A (zh) * 2018-09-11 2019-01-04 中山大学 一种血液流量测量设备及方法
CN109363627A (zh) * 2018-11-29 2019-02-22 中山大学 一种血液流速的测量装置及方法
CN110638466B (zh) * 2019-09-17 2022-06-03 广东普洛宇飞生物科技有限公司 一种定位装置及方法
CN112022085B (zh) * 2020-09-16 2022-04-15 中山大学 一种视网膜内的血管流量的计算方法

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
CN101243966A (zh) * 2008-03-21 2008-08-20 中国科学院光电技术研究所 一种高分辨率眼底血管流速测量系统及测量方法
JP2009165710A (ja) * 2008-01-17 2009-07-30 Univ Of Tsukuba 眼底血流量の定量測定装置
WO2010143601A1 (fr) * 2009-06-11 2010-12-16 国立大学法人筑波大学 Appareil de tomographie à cohérence optique à deux faisceaux
CN103002794A (zh) * 2010-02-08 2013-03-27 奥勒冈保健科学大学 用于超高灵敏光学微血管显影术之设备及方法
US20140073917A1 (en) * 2012-09-10 2014-03-13 Oregon Health & Science University Quantification of local circulation with oct angiography
CN104168823A (zh) * 2014-02-28 2014-11-26 深圳市斯尔顿科技有限公司 一种血液流速的测量装置及方法

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2009165710A (ja) * 2008-01-17 2009-07-30 Univ Of Tsukuba 眼底血流量の定量測定装置
CN101243966A (zh) * 2008-03-21 2008-08-20 中国科学院光电技术研究所 一种高分辨率眼底血管流速测量系统及测量方法
WO2010143601A1 (fr) * 2009-06-11 2010-12-16 国立大学法人筑波大学 Appareil de tomographie à cohérence optique à deux faisceaux
CN103002794A (zh) * 2010-02-08 2013-03-27 奥勒冈保健科学大学 用于超高灵敏光学微血管显影术之设备及方法
US20140073917A1 (en) * 2012-09-10 2014-03-13 Oregon Health & Science University Quantification of local circulation with oct angiography
CN104168823A (zh) * 2014-02-28 2014-11-26 深圳市斯尔顿科技有限公司 一种血液流速的测量装置及方法

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP3305187A4 (fr) * 2015-05-27 2019-02-13 Shenzhen Certainn Technology Co., Ltd. Appareil et procédé permettant de mesurer le débit sanguin dans un vaisseau sanguin
US10456033B2 (en) 2015-05-27 2019-10-29 Shenzhen Certainn Technology Co., Ltd. Apparatus and method for measuring blood flow of vessels

Also Published As

Publication number Publication date
CN104159505A (zh) 2014-11-19
CN104159505B (zh) 2016-03-09

Similar Documents

Publication Publication Date Title
WO2015172322A1 (fr) Dispositif et procédé de détection de la quantité d'écoulement sanguin
US7480059B2 (en) Optical coherence tomography for eye-length measurement
JP7057186B2 (ja) 眼科装置、及び眼科情報処理プログラム
US9820645B2 (en) Ophthalmologic apparatus
JP6465551B2 (ja) 光干渉眼寸法測定装置
WO2016188178A1 (fr) Appareil et procédé permettant de mesurer le débit sanguin dans un vaisseau sanguin
CN111265183B (zh) 基于光束平行扫描模式的视网膜血流测量装置
CN109124686A (zh) 一种血液流量测量设备及方法
WO2015127661A1 (fr) Dispositif et procédé de mesure de la vitesse d'écoulement du sang
CN112244760A (zh) 基于分光棱镜实现眼前节oct整合生物测量仪功能的成像装置
TWI463130B (zh) 光學裝置及其運作方法
CN113995374A (zh) 一种全眼球三维成像装置及方法
CN109363627A (zh) 一种血液流速的测量装置及方法
US20230218167A1 (en) Ophthalmic apparatus
WO2013085042A1 (fr) Dispositif d'observation de fond d'œil
CN204708834U (zh) 一种测量血管血液流量的设备
CN213309629U (zh) 一种眼球成像装置以及眼球血液流速测量装置
US11497397B2 (en) Ophthalmologic apparatus
CN111557637B (zh) 眼科测量系统
WO2015172581A1 (fr) Appareil et procédé de mesure de flux sanguin
CN105310677B (zh) 一种测量血液流量的设备及方法
JP2020130266A (ja) 眼科装置
US11298019B2 (en) Ophthalmologic apparatus and method for controlling the same
US11896307B2 (en) Ophthalmologic apparatus and method of controlling same
JP7530252B2 (ja) 眼科装置及びその制御方法

Legal Events

Date Code Title Description
WWE Wipo information: entry into national phase

Ref document number: 201480000246.7

Country of ref document: CN

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

Ref document number: 14891788

Country of ref document: EP

Kind code of ref document: A1

NENP Non-entry into the national phase

Ref country code: DE

122 Ep: pct application non-entry in european phase

Ref document number: 14891788

Country of ref document: EP

Kind code of ref document: A1