WO1999016366A1 - Bubble detection - Google Patents
Bubble detection Download PDFInfo
- Publication number
- WO1999016366A1 WO1999016366A1 PCT/US1998/020622 US9820622W WO9916366A1 WO 1999016366 A1 WO1999016366 A1 WO 1999016366A1 US 9820622 W US9820622 W US 9820622W WO 9916366 A1 WO9916366 A1 WO 9916366A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- laser
- bubble
- distal end
- light
- ofthe
- Prior art date
Links
Classifications
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01M—TESTING STATIC OR DYNAMIC BALANCE OF MACHINES OR STRUCTURES; TESTING OF STRUCTURES OR APPARATUS, NOT OTHERWISE PROVIDED FOR
- G01M3/00—Investigating fluid-tightness of structures
- G01M3/02—Investigating fluid-tightness of structures by using fluid or vacuum
- G01M3/04—Investigating fluid-tightness of structures by using fluid or vacuum by detecting the presence of fluid at the leakage point
- G01M3/06—Investigating fluid-tightness of structures by using fluid or vacuum by detecting the presence of fluid at the leakage point by observing bubbles in a liquid pool
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
- G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
- G01N21/41—Refractivity; Phase-affecting properties, e.g. optical path length
- G01N21/43—Refractivity; Phase-affecting properties, e.g. optical path length by measuring critical angle
- G01N21/431—Dip refractometers, e.g. using optical fibres
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
- A61B18/22—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor
- A61B18/26—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser the beam being directed along or through a flexible conduit, e.g. an optical fibre; Couplings or hand-pieces therefor for producing a shock wave, e.g. laser lithotripsy
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/18—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves
- A61B18/20—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by applying electromagnetic radiation, e.g. microwaves using laser
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00017—Electrical control of surgical instruments
- A61B2017/00022—Sensing or detecting at the treatment site
- A61B2017/00057—Light
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
- A61B17/22004—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for using mechanical vibrations, e.g. ultrasonic shock waves
- A61B2017/22005—Effects, e.g. on tissue
- A61B2017/22007—Cavitation or pseudocavitation, i.e. creation of gas bubbles generating a secondary shock wave when collapsing
- A61B2017/22008—Cavitation or pseudocavitation, i.e. creation of gas bubbles generating a secondary shock wave when collapsing used or promoted
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B2018/00636—Sensing and controlling the application of energy
Definitions
- the photoelectric detectors may be positioned in the liquid adjacent the predetermined locations or positioned out of the liquid and coupled to the predetermined locations by fiber optic cables.
- a laser beam can be directed across the predetermined location and received by a detector on the opposite side of the laser source. When a bubble interrupts the laser beam, a signal is generated.
- U.S. Patent No.4,662,749 titled "Fiber Optic Probe And System For Particle Size And Velocity Measurement” discloses a system for the simultaneous measurement of the size and velocities of bubbles or drops in a multiphase process environment wherein light passing through a Ronchi grating is projected onto a measurement volume within the multiphase process stream by a coherent fiber optic bundle and a gradient index imaging lens. Drops or bubbles passing through the measurement volume reflect or refract light which is sensed by velocity and size sensor fiber optic bundles disposed opposite the imaging lens and the sensed signal is coupled to signal processing means which convert the light signal to electrical signals.
- the appropriate size velocity measurements are made using one or more of the visibility techniques, phase lag techniques or transit time techniques.
- Figure 1 shows an embodiment of the present invention.
- Figure 2A shows the typical output from the detector of Figure 1 during bubble formation and collapse.
- Figure 6B depicts the ultrasonic dissolution of a blockage using an adjunct fluid.
- Figures 8A-C depict the superheated vapor expansion mode as a method of bubble formation.
- PET ATT .ED DESCRTPTTON OF THE TNVFNTTON Although this invention may be used for a variety of bubble detection applications, it is discussed in light of medical applications, where a bubble is formed at a remote location within the body. Many bubble detection methods exist but are impractical for this application. Optical methods have been used to detect bubbles, often collecting light from the side opposite to the emission signal. In the present invention, light may be delivered and collected from the same optical fiber, eliminating the need to cross an occlusion and allowing for remote and minimally invasive access. Further, the same optical fiber used for delivering therapeutic radiation can be used for the bubble detection mechanism.
- some light is scattered back into the fiber, depending on the optical properties, (scattering coefficient, absorption coefficient, and anisotropy), of the material at the distal end.
- This reflected and scattered feedback light is measured at the proximal end of the same fiber, allowing remote access to the treated area.
- the DC level of the measured signal depends on the material at the output of the fiber.
- the AC component of the signal corresponds to the bubble dynamics. Time of growth and collapse, and the size of the generated bubble or bubbles, can be determined. Because the feedback signal is dependent on the material's optical properties, feedback signals at multiple wavelengths can be used as a method for identifying different types of tissue.
- a laser system provides a laser beam 10 for bubble generation. This beam is reflected from a dichroic mirror or beamsplitter 12, passes through beamsplitter 14 (or a mirror 14 with a hole), and is focused by lens 16 into the proximal end of fiber optic 18. The distal end of this fiber is positioned for the delivery of laser light into a medium, such as near a thrombus within the vasculature.
- a second laser system provides a laser beam 20 for bubble detection. Laser beam 20 passes through beamsplitters 12 and 14 and is focused by lens 16 into fiber optic 18.
- a properly oriented linear polarizer 28 rejects the linearly polarized reflected laser light from these surfaces while transmitting the randomly polarized light emerging from the optical fiber 18.
- a component of laser beam 10 also propagates back toward beamsplitter 14, to be focused by lens 22 and passed through polarizer 28.
- Filter 24 eliminates a portion of this bubble generating light.
- Grating 26 spatially separates the two wavelengths produced one each by laser beam 10 and laser beam 20.
- Detector 30 is generally positioned to receive light only from laser beam 20.
- the use of additional probing wavelengths would make tissue discrimination easier as different wavelengths can have dramatically different optical properties (index of refraction, absorption, scattering, anisotropy) in tissues.
- the returned and detected signals from two or more probing wavelengths can be ratioed to give an indication of material type. For example, to discriminate whether a probe is immersed in blood or proximal to an artery wall, a wavelength strongly absorbed by blood (blue wavelength) and a wavelength poorly absorbed by both (red) may be used. When the fiber is immersed in blood, the ratio of the red light to the strongly absorbed and less scattering blue light should be greater than when the fiber is abutting the vessel.
- a 'smart' laser system could be provided these data to determine which tissue is being irradiated and alter the irradiation parameters (wavelength, pulse duration, energy/pulse, power, etc.) to achieve a desired effect or prevent undesirable consequences.
- a laser could be tuned to match the strongest absorption of the target material or could be disabled when an inappropriate target is present.
- a computer could be used to interpret this data and control the laser or these tasks could be performed by timing, level detection, and logic circuits.
- Applications envisioned for this invention include any method or procedure where the detection of vapor or cavitation bubbles is desirable. Applications may include bubble diagnostic and/or feedback mechanism during:
- Laser-based treatment e.g. Optical Acoustic Thrombolysis
- This technology can lyse thrombus and lead to reperfusion of the affected cerebral tissue.
- Laser-based treatment e.g. Optical Acoustic Thrombolysis
- This technology can relax vaso-constriction leading to restoration of normal perfusion and therefore prevent further transient ischemic attacks or other abnormal perfusion situations.
- Laser-based treatment e.g. Optical Acoustic Thrombolysis
- This technology can lyse thrombus or remove atherosclerotic plaque from arteries.
- Laser-based treatment e.g. Optical Acoustic Thrombolysis
- stenoses of the carotid arteries • Laser-based treatment (e.g. Optical Acoustic Thrombolysis) of stenoses of the carotid arteries.
- An embodiment of the invention incorporates a catheter containing an optical fiber.
- the optical fiber is coupled at the proximal end to a high repetition rate laser system which injects pulses of light along the beampath of laser beam 110 as described in Figure 1.
- the light emerging from the fiber at the distal end is absorbed by the fluid surrounding the catheter.
- This fluid may be blood, a biological saline solution containing an absorbing dye, a thrombolytic pharmaceutical or thrombus itself.
- the optical fiber functions as a means of energy transmission such that the optical energy produced by the laser is delivered to the end of the fiber.
- Lysis of thrombus, atherosclerotic plaque or any other occluding material in the tubular tissue is facilitated by an ultrasonic radiation field created in the fluids near the occlusion.
- a working channel which surrounds or runs parallel to the optical fiber may be used to dispense small quantities of thrombolytic drugs to facilitate further lysis of any significantly sized debris (>5 ⁇ m dia. particles) left over from the acoustic thrombolysis process.
- the conversion of optical to acoustic energy may proceed through several mechanisms that may be thermoelastic, thermodynamic or a combination of these.
- Typical operation leads to a fluid-based transducer that cycles at 1 - 100 kHz with a reciprocating displacement of 100-200 ⁇ m (for typical optical fiber dimensions). This displacement is very similar to that found in mechanically-activated ultrasound angioplasty devices.
- each laser pulse 140 delivers a controlled level of energy in the fluid within an absorption depth which is very small compared to the characteristic size of the vessel containing the catheter, or even small compared to the fiber diameter.
- the absorption depth may also be small compared to the distance that a sound wave travels in the duration ofthe laser pulse.
- the laser energy deposits a sufficient level of energy to heat most ofthe fluid within the absorption depth well above the vaporization temperature of the fluid at the ambient pressure.
- a thermoelastically-generated acoustic wave is launched in the fluid, which propagates out from the heated region.
- the superheated fluid 142 undergoes vaporization, which creates a bubble of vapor.
- its volume 144 increases by a large factor.
- the laser pulse duration need not be restricted to times as short as in the thermoelastic mode since the bubble expansion is nearly an isobaric process; however, the laser pulse duration should be shorter than the bubble expansion time, and it should be much shorter than a typical thermal relaxation time for the superheated region. (According to the Rayleigh bubble collapse theory the bubble lifetime in water is approximately 25 ⁇ s for a 50 ⁇ m diameter bubble; thermal relaxation occurs on a few hundred microsecond time scale, so the laser pulse should be several microseconds or less in duration).
- the vapor bubble expands up to a maximum radius which depends on the vapor pressure initially created in the fluid and the fluid properties.
- These opto-acoustic modes of coupling laser energy into acoustic excitations in tissues include a number of features. Low to moderate laser pulse energy combined with high repetition rate avoids excessive tissue heating or intense shock generation. Localized absorption ofthe laser energy occurs. Laser energy may interact thermoelastically or thermodynamically with the ambient fluids. An acoustic radiation field is generated by repeated expansion and collapse of a bubble at the tip ofthe fiber. Resonant operation may be achieved by matching the laser pulse period to the lifetime of the generated bubble. Soft fibrous occlusions (thrombus) may be disrupted by generating the bubbles directly within the thrombus.
- thrombus Soft fibrous occlusions
- Control and/or manipulation ofthe spatial and temporal distribution of energy deposited in the fluid at the fiber tip can be used to modify the near field acoustic radiation pattern, for example, to concentrate acoustic energy on an object in proximity to the fiber, or to distribute the acoustic radiation more uniformly.
- Techniques based on this strategy will be most successful for a special case of thermoelastic response (first mode) where the laser pulse duration is short and the fluid absorption is also relatively strong, such that the laser energy is deposited in a thin layer adjacent to the surface ofthe fiber tip. For example, by forming a concave surface on the fiber tip, the optical energy is deposited in the fluid in a similar shaped distribution.
- Tunability over a wide spectrum provides a broad range of flexibility for matching the laser wavelength to the absorption characteristics ofthe fluids located at the distal end ofthe catheter.
- the output beam is coupled by an optical fiber to the surgical site through, for example, a percutaneous catheter.
- a pulsed beam of light drives the ultrasonic excitation which removes and/or emulsifies thrombus or atherosclerotic plaque with less damage to the underlying tissue and less chance of perforating the blood vessel wall than prior art devices.
- Suitable dyes for use in the dye laser components of the invention include, for example, P-terphenyl (peak wavelength 339); BiBuQ (peak wavelength: 385); DPS (peak wavelength: 405); and Coumarin 2 (peak wavelength: 448).
Abstract
Description
Claims
Priority Applications (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
CA002306561A CA2306561A1 (en) | 1997-09-30 | 1998-09-29 | Bubble detection |
KR1020007003481A KR20010030829A (en) | 1997-09-30 | 1998-09-29 | Bubble detection |
AU95961/98A AU9596198A (en) | 1997-09-30 | 1998-09-29 | Bubble detection |
JP2000513512A JP2001517805A (en) | 1997-09-30 | 1998-09-29 | Bubble detection method |
EP98949688A EP1018952A1 (en) | 1997-09-30 | 1998-09-29 | Bubble detection |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/941,015 US6538739B1 (en) | 1997-09-30 | 1997-09-30 | Bubble diagnostics |
US08/941,015 | 1997-09-30 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1999016366A1 true WO1999016366A1 (en) | 1999-04-08 |
Family
ID=25475797
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1998/020622 WO1999016366A1 (en) | 1997-09-30 | 1998-09-29 | Bubble detection |
Country Status (8)
Country | Link |
---|---|
US (1) | US6538739B1 (en) |
EP (1) | EP1018952A1 (en) |
JP (1) | JP2001517805A (en) |
KR (1) | KR20010030829A (en) |
CN (1) | CN1279595A (en) |
AU (1) | AU9596198A (en) |
CA (1) | CA2306561A1 (en) |
WO (1) | WO1999016366A1 (en) |
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US6368318B1 (en) | 1998-01-23 | 2002-04-09 | The Regents Of The University Of California | Opto-acoustic recanilization delivery system |
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Also Published As
Publication number | Publication date |
---|---|
KR20010030829A (en) | 2001-04-16 |
CN1279595A (en) | 2001-01-10 |
AU9596198A (en) | 1999-04-23 |
US6538739B1 (en) | 2003-03-25 |
CA2306561A1 (en) | 1999-04-08 |
EP1018952A1 (en) | 2000-07-19 |
JP2001517805A (en) | 2001-10-09 |
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