Source: https://patents.google.com/patent/WO2004096049A2/en
Timestamp: 2019-03-24 02:59:05
Document Index: 769447883

Matched Legal Cases: ['art 31', 'art 31', 'art 31', 'art 31', 'art 31', 'art 31', 'art 31', 'art.\n21', 'art.\n33', 'art.\n57']

WO2004096049A2 - Catheter imaging probe and method - Google Patents
WO2004096049A2
WO2004096049A2 PCT/US2004/012773 US2004012773W WO2004096049A2 WO 2004096049 A2 WO2004096049 A2 WO 2004096049A2 US 2004012773 W US2004012773 W US 2004012773W WO 2004096049 A2 WO2004096049 A2 WO 2004096049A2
PCT/US2004/012773
WO2004096049A3 (en
2004-04-23 Application filed by Board Of Regents, The University Of Texas System filed Critical Board Of Regents, The University Of Texas System
2004-11-11 Publication of WO2004096049A2 publication Critical patent/WO2004096049A2/en
2004-12-02 Publication of WO2004096049A3 publication Critical patent/WO2004096049A3/en
2006-10-20 Priority claimed from US11/551,684 external-priority patent/US7853316B2/en
2006-12-06 Priority claimed from US11/567,244 external-priority patent/US7844321B2/en
The probe (100) comprises a conduit (110) through which energy is transmitted having a first portion (120) through which the conduit (110) extends and a second portion (130) which rotates relative to conduit (110) to redirect the energy from the conduit (110).
Myocardial infarction or heart attack remains the leading cause of death in our society. Unfortunately, most of us can identify a family member or close friend that has suffered from a myocardial infarction. Until recently many investigators believed that coronary arteries critically blocked with atherosclerotic plaque that subsequently progressed to total occlusion was the primary mechanism for myocardial infarction. Recent evidence from many investigational studies, however, clearly indicate that most infarctions are due to sudden rupture of non-cri ticall v stenosed coronary arteries due to sudden plaque rupture. For example, Little and coworkers (Little, WC, Downes, TR, Applegate, RJ. The underlying coronary lesion in myocardial infarction: implications for coronary angiography. Clin Cardiol 1991; 14: 868-874, incorporated by reference herein) observed that approximately 70% of patients suffering from an acute plaque rupture were initiated on plaques that were less than 50% occluded as revealed by previous coronary angiography. This and similar observations have been confirmed by other investigators (Nissen, S. Coronary angiography and intravascular ultrasound. Am J Cardiol 2001; 87 (suppl) : 15A - 20 A, incorporated by reference herein) .
The unstable plaque was first identified and characterized by pathologists in the early 1980' s. Davis and coworkers noted that with the reconstruction of serial histological sections in patients with acute myocardial infarctions associated with death, a rupture or fissuring of atheromatous plaque was evident (Davis MJ, Thomas AC. Plaque fissuring: the cause of acute myocardial infarction, sudden death, and crescendo angina. Br Heart J 1985; 53: 363-373, incorporated by reference herein) . Ulcerated plaques were further characterized as having a thin fibrous cap, increased macrophages with decreased smooth muscle cells and an increased lipid core when compared to non-ulcerated atherosclerotic plaques in human aortas (Davis MJ, Richardson PD, oolf N, Katz DR, Mann J. Risk of thrombosis in human atherosclerotic plaques: role of extracellular lipid, macrophage, and smooth muscle cell content, incorporated by reference herein) . Furthermore, no correlation in size of lipid pool and percent stenosis was observed when imaging by coronary angiography. In fact, most cardiologists agree that unstable plaques progress to more stenotic yet stable plaques through progression via rupture with the formation of a mural thrombus and plaque remodeling, but without complete luminal occlusion (Topol EJ, Rabbaic R. Strategies to achieve coronary arterial plaque stabilization. Cardiovasc Res 1999; 41: 402-417, incorporated by reference herein). Neo- vascularization with intra-plaque hemorrhage may also play a role in this progression from small lesions (<50% occluded) to larger significant plaques. Yet, if the unique features of unstable plaque could be recognized by the cardiologist and then stabilized, a dramatic decrease may be realized in both acute myocardial infarction and unstable angina syndromes, and in the sudden progression of coronary artery disease.
The present invention uses depth-resolved light reflection or Optical Coherence Tomography (OCT) to identify the pathological features that have been identified in the vulnerable plaque. In OCT, light from a broad band light source is split by an optical fiber splitter with one fiber directing light to the vessel wall and the other fiber directing light to a moving reference mirror. The distal end of the optical fiber is interfaced with a catheter for interrogation of the coronary artery during a heart catheterization procedure. The reflected light from the plaque is recombined with the signal from the reference mirror forming interference fringes (measured by an photovoltaic detector) allowing precise depth-resolved imaging of the plaque on a micron scale.
OCT uses a superluminescent diode source emitting a 1300 nm wave length, with a 50 nm band width (distribution of wave length) to make in situ tomographic images with axial resolution of 10 - 20 μm and tissue penetration of 2 - 3 mm. OCT has the potential to image tissues at the level of a single cell. In fact, the inventors have recently utilized broader band width optical sources such as femto-second pulsed lasers, so that axial resolution is improved to 4 μm or less. With such resolution, OCT can be applied to visualize intimal caps, their thickness, and details of structure including fissures, the size and extent of the underlying lipid pool and the presence of inflammatory cells. Moreover, near infrared light sources used in OCT instrumentation can penetrate into heavily calcified tissue regions characteristic of advanced coronary artery disease. With cellular resolution, application of OCT may be used to identify other details of the vulnerable plaque such as infiltration of monocytes and acrophages . In short, application of OCT can provide detailed images of a pathologic specimen without cutting or disturbing the tissue.
One concern regarding application of this technology to image atherosclerotic plaques within the arterial lumen is the strong scattering of light due to the presence of red blood cells. Once a catheter system is positioned in a coronary artery, the blood flow between the OCT optical fiber and artery can obscure light penetration into the vessel wall. One proposed solution is the use of saline flushes. Saline use is limited in duration, however, since myocardial ischemia eventually occurs in the distal myocardium. The inventors have proposed the use of artificial hemoglobin in the place of saline. Artificial hemoglobin is non-particulate and therefore does not scatter light. Moreover, artificial hemoglobin is about to be approved by the United States Food and Drug Administration as a blood substitute and can carry oxygen necessary to prevent myocardial ischemia. Recently, the inventors demonstrated the viability of using artificial hemoglobin to reduce light scattering by blood in mouse myocardium coronary arteries (Villard JW, Feldman MD, Kim Jeehyun, Milner TE, Freeman GL. Use of a blood substitute to determine instantaneous murine right ventricular thickening with optical coherence tomography. Circulation 2002; Volume 105: Pages 1843-1849, incorporated by reference herein) .
The first prototype of an OCT catheter to image coronary plaques has been built and is currently being tested by investigators in Boston at Harvard - MIT (Jang IK, Bouma BE, Kang DH, et al . Visualization of coronary atherosclerotic plaques in patients using optical coherence tomography: comparison with intravascular ultrasound. JACC 2002; 39: 604- 609, incorporated by reference herein) in association with Light Lab Co. The prototype catheter consists of a single light source and is able to image over a 360 degree arc of a coronary arterial lumen by rotating a shaft that spins the optical fiber. Because the rotating shaft is housed outside of the body, the spinning rod in the catheter must rotate with uniform angular velocity so that the light can be focused for equal intervals of time on each angular segment of the coronary artery. Mechanical drag in the rotating shaft can produce significant distortion and artifacts in recorded OCT images of the coronary artery. Unfortunately, because the catheter will always be forced to make several bends between the entry point in the femoral artery to the coronary artery (e.g., the 180 degree turn around the aortic arch) , uneven mechanical drag will result in OCT image artifacts As the application of OCT is shifted from imaging gross anatomical structures of the coronary artery to its capability to image at the level of a single cell, non- uniform rotation of the single fiber OCT prototype will become an increasingly problematic source of distortion and image artifact.
Essentially, current endoscope type single channel OCT systems developed by Light Lab Co. suffers by non-constant rotating speed that forms irregular images of a vessel target. See U.S. Patent 6,134,003, incorporated by reference herein. Their approach of a rotary shaft to spin a single mode fiber is prone to produce artifact. The catheter will always be forced to make several bends from its entry in the femoral artery, to the 180 degree turn around the aortic arch, to its final destination in the coronary artery. All these bends will cause uneven friction on the rotary shaft, and uneven time distribution of the light on the entire 360 degree arch of the coronary artery. As the application of OCT is shifted from gross anatomical structures of the coronary artery to its capability to image at the level of a single cell, then non-uniform rotation of the single fiber OCT will become even a greater source of greater artifact.
The present invention pertains to a method for imaging a patient. The method comprises the steps of inserting a catheter into the patient. There is the step of rotating a second portion of the catheter relative to a conduit extending through a first portion of the catheter, which redirects the energy transmitted through the conduit to the patient and receives the energy reflected back to the second portion from the patient and redirects the reflected energy to the conduit .
Figure 1 is a schematic representation of the present invention.
Figure 2 is a cross-section of 2-2 of figure 1.
Figure 3 is a cross-section of 3-3 of figure 1.
Figure 4 is a cross-section of 4-4 of figure 1.
Figure 5 is a schematic representation of a capsule . Figure 6 is a schematic representation of a side view of a wheel.
Figure 7 is a schematic representation of an axial view of the wheel.
Figure 8 is a schematic representation of a side view of the mill.
Figure 9 is a schematic representation of an axial view of the mill.
Figures 10a and 10b are schematic representations of a screw embodiment.
Figure 11 is a schematic representation of an exploded view of a mass flow embodiment.
Figure 12 is a schematic representation of electric field direction.
Figure 13 is a schematic representation of an exploded view of another mass flow embodiment.
Figures 14a and 14b are schematic representations of an exploded view of deformable material as the media.
Figure 15 is a schematic representation of an exploded view of another deformable material embodiment. Figures 16a and 16b are schematic representations of an electrostatic force embodiment.
Figure 17 is a schematic representation of a nanorotor-nanostator embodiment generally.
Referring now to the drawings wherein like reference numerals refer to similar or identical parts throughout the several views, and more specifically to figure 1 thereof, there is shown a catheter imaging probe 100 for a patient. The probe 100 comprises a conduit 110 through which energy is transmitted. The probe 100 comprises a first portion 120 through which the conduit 110 extends. The probe 100 comprises a second portion 130 which rotates relative to the conduit 110 to redirect the energy from the conduit 110.
Preferably, the first portion 120 includes an inlet tube 1 through which fluid flows and wherein the second portion 130 is turned by flowing fluid from the inlet tube 1. The second portion 130 preferably includes a turbine 4 which is turned by the flowing fluid. Preferably, the turbine 4 includes a rotating center shaft 20 through which the conduit 110 extends, and spiral shaped inner grooves 22 which extend from the center shaft 20 that provide a rotating torque to the center shaft 20 when the flowing fluid flows against the grooves 22 that causes the center shaft 20 to rotate about the conduit 110. ■ l l -
Preferably, the second portion 130 includes a cover transparent to the energy which encapsulates the cylinder and contacts the first portion 120 so no fluid can escape from the second portion 130 except through the outlet tube 2. The second portion 130 preferably includes a cylinder attached to the first portion 120 from which the knobs 5 extend and that defines a chamber which fluid from the inlet tube 1 flows through. The turbine 4 is disposed in the chamber. Preferably, the second portion 130 includes an energy field reshaping component, such as a lens 11, which focuses the energy onto the patient. The lens 11 can be a microlens, grin lens, or optical fiber lens. The probe 100 preferably includes a fluid source 26 connected to the inlet tube 1. Preferably, the fluid in the fluid source 26 is chosen from the group consisting of nitrogen, helium, saline, water, D5W or artificial blood. The first portion 120 is solid except for the conduit 110 and the inlet and outlet tubes 1, 2. Preferably, the turbine 4 includes a wart 31 which reflects energy coming through a radiation energy guide 30 back to the radiation energy guide 30 (another optical fiber preferably) . The wart 31 rotates with the second portion 130. The energy reflected by the wart 31 indicates current angular position of the second portion 130. The wart 31 identifies one angular position (not all the positions) of the rotating portion when the light hits and gets back from the wart 31. In this way, it is known the shaft 20 rotates one cycle and also the starting position of the acquired image on the vessel wall. The wart 31 is preferably a block shape with a flat wall facing the radiation energy guide 30, to reflect the energy back. It is preferably molded into the shaft 10, and the flat wall can have a reflective material, such as a mirror placed on it to increase the reflection. The width of the wart is small compared to the circumference of the shaft 20, so as to identify a given point, and is high enough to block the energy emitted from radiation energy guide 30, so it is reflected by the wart 31..
The present invention pertains to a method for imaging a patient. The method comprises the steps of inserting a catheter into the patient. There is the step of rotating a second portion 130 of the catheter relative to a conduit 110 extending through a first portion 120 of the catheter, which redirects the energy transmitted through the conduit 110 to the patient and receives the energy reflected back to the second portion 130 from the patient and redirects the reflected energy to the conduit 110. Preferably, the rotating step includes the step of flowing fluid through an inlet tube 1 to the second portion 130 to turn the second portion 130. The following step preferably includes the step of flowing fluid through the inlet tube 1 to turn a turbine 4 of the second portion 130. Preferably, the flowing step includes the step of flowing the fluid against spiral shaped inner grooves 22 which extend from a rotating center shaft 20 of the turbine 4 to create a rotating torque on the center shaft 20 that causes the center shaft 20 to rotate about the conduit 110 that extends through the center shaft 20. The second portion 130 preferably has a reflecting material 24 attached to the center shaft 20 which redirects the energy from the conduit 110. Preferably, the conduit 110 is an optical fiber 3.
The reflecting material 24 preferably includes a prism 8 or mirror which reflects light from the conduit 110, and including the step of rotating the prism 8 with the center shaft 20 as the center shaft 20 is rotated by the flowing fluid. Preferably, the rotating step includes the step of rotating the center shaft 20 that is supported by knobs 5 of a cylinder of the turbine 4 in which the center shaft 20 is disposed. The flowing step preferably includes the step of flowing the fluid from the inlet tube 1 through the chamber of the cylinder. Preferably, the flowing step includes the step of removing the fluid flowing from the cylinder of the second portion 130 through at least one outlet tube 2 that extends through the first portion 120. In the operation of the invention, figure 1 shows the diagram of turbine 4 based catheter type imaging probe 100 which may be connected to sample arm of single mode fiber 3 OCT. Figures 2, 3 and 4 are cross-sectional images of the probe 100 at cross-section (1), (2), (3). At the center of the probe 100, there is a turbine 4 which is connected to a prism 8. Gas or liquid flows through an outlet tube 2 into the turbine 4 chamber. The turbine 4 is supported by knobs 5 to maintain constant position during rotation. At the center of the turbine 4, there is a hole to place an optical fiber 3 that is glued onto a cylinder 9. During the rotation of the turbine 4, the optical fiber 3 will not move or rotate at all. All of these parts are capsulated by outmost transparent cover 10. The material for this transparent cover can be any biocompatible polymers (e.g. plastic Tygon). Probing light will be launched from the single mode optical fiber 3 through a lens 11 having a curvature to focus the light onto target tissue area. A rotating prism 8 connected to the turbine 4 reflects incoming light toward target tissue area on the vessel wall. The reflected light from the target tissue goes back into the fiber 3 through the prism 8. A standard analysis on the light is then performed to obtain the image. See U.S. Patent 6,134,003, incorporated by reference herein. Gas or liquid gone through the turbine 4 exits the probe 100 through an outlet tube 2. Rotation direction and speed of the second portion are controlled by the pressure difference between the inlet 1 and outlet 2.
Gas: Nitrogen, Helium, C02 or any gas that can be dissolved into blood or tissue relatively easily.
Outer diameter of transparent cover 10: 1.2mm
Outer diameter of cylinder 9: 0.8mm
Outer diameter of inlet tube 1: 0.2mm
Outer diameter of outlet tube 2: 0.2mm
Outer diameter of fiber 3: 0.125mm Preferred Characteristics
Turbine length: 0.5mm
Turbine area: 0.35A2*pi=0.38mm2
Volume of the inner cylinder for the turbine: 0.38*0.5=0.19mm3
Target flow rate: 0.19 mrtvVsec
In an alternative preferred embodiment shown in figures 5-9, the second portion 130 includes a mill 50. The mill 50 preferably includes a wheel 52. Preferably, the mill 50 includes a capsule 54 which holds the wheel 52. The conduit 54 is preferably an optical fiber 3. Preferably, the wheel 52 includes a plug 56, and fins 58 which extend radially from the plug 56. The plug 56 has a hole at the center which receives the optical fiber. The fins 58 are pushed by the fluid causing the plug 56 to rotate.
The second portion 130 preferably includes a cover
33 transparent to the energy which encapsulates the capsule 54 and contacts or attaches to the first portion 120 so no fluid can escape from the second portion 130 except through the outlet tube 2. The cover 333 can be glued to the first portion. Alternatively, the cover 33 can be of a long enough length that it extends the length of the first portion and the second portion. During assembly, after the mill (or for that matter the turbine) is connected to the first portion, then the mill and the first portion are inserted into the cover, which is basically a long hollow transparent tube with a closed end. The mill on the end of the first portion is then feed through the tube until it is in place at the end of the tube. The flexible tube can be of such an inner diameter that it forms a tight fit with the outer circumference of the first portion and prevents fluid from escaping the end about the mill except through the outlet port .
The probe 100 preferably includes a fluid source 26 connected to the inlet tube 1. Preferably, the fluid in the fluid source 26 is chosen from the group consisting of nitrogen, helium, C02, saline, water, D5W, ringers lactate or artificial blood.
Preferably, the following step includes the step of flowing fluid through the inlet tube 1 to turn a wheel 52 of a mill 50 of the second portion 130. The flowing step preferably includes the step of flowing the fluid against fins 58 which extend from a rotating plug 56 of the wheel 52 to cause the wheel 52 to rotate about the conduit 54 that extends through the plug 56. Preferably, the second portion 130 has a reflecting material 24 attached to the plug 56 which redirects the energy from the conduit 54. The conduit 54 preferably is an optical fiber 3. Preferably, the reflecting material 24 includes a prism 8 which reflects light from the conduit 54, and including the step of rotating the prism 8 with the plug 56 as the wheel 52 is rotated by the flowing fluid. Rotating direction and speed of the second portion are controlled by the pressure difference between the inlet and outlet 60, 62.
In the operation of the alternative preferred embodiment, and referring to figures 5-9, the probe 100 is introduced into the patient through the femoral artery, as is well known in the art, and moved to a desired location in regard to the heart by standard catheterization techniques. Once the probe 100 is at the desired location, a gas, such as nitrogen, C02 or helium or any gas that can be dissolved into tissue relatively easily or a liquid, such as saline, D5W, lactated ringers or artificial blood (oxyglobin) , is introduced from the fluid source 26 to the inlet tube 1 in the first portion 120 of the probe 100. The first portion 120 of the probe 100 is essentially solid except for the inlet tube 1, and an outlet tube 2 and the optical fiber 3, which extend through the first portion 120.
The second portion 130 is in the form of a mill 50 with a wheel 52 disposed in a capsule 54. The wheel 52 comprises a plug 56 having a hollow central axis through which the optical fiber 3 extends, and fins 58 that extend radially outward from the plug 56. A first end 64 of the plug 56 is disposed in a first pocket 68 of the capsule 54, and a second end 66 of the plug 56 is disposed in a second end 66 pocket of the capsule 54. The first and second pockets 68, 70 maintain the plug 56 in a desired location in the capsule 54, while allowing the plug 56 to freely rotate inside the capsule 54. The plug 56 with the fins 58 is introduced to the capsule 54 by a cap of the capsule 54 being removed so the plug 56 can be introduced into the body of the capsule 54. The end of the cap is then fitted back on the body with the first end 64 of the plug 56 disposed in the first pocket 68 and the second end 66 of the plug 56 disposed in the second pocket 70 that is found in the cap.
As shown in figures 10a and 10b, a screw embodiment can also be used, with fluid flow direction moving the screw forward or back depending on the direction of the fluid flow.
See figure 17 for reference to the following descriptions regarding different embodiments of nanotechnology based probe tips. >
If the media is a solution, a mass flow can be generated in the solution to provide the torque actuating the rotor, as shown in figure 11. The flow-actuated turbine that is desirable above is one example. In that case, the mass flow is the flow of the flowing fluid. Mass flow could be ions flow. When the media is a kind of electrolyte, such as NaCl solution, an electric field can be provided to make the ions, such as Na+ and Cl", move toward opposite directions. The mass flow generated from the movement of the ions would provide a net momentum that make the solvent, that is, the water flow. An electric field that surrounds the shaft of the nanomotor makes it strong enough to affect the media electrolyte between the stator and the rotor, the water in the media electrolyte will flow around the shaft such that a torque will be generated between the stator and the rotor. Furthermore, with obstacle structures, such as fans, on the rotor, the torque will be more sufficiently used. The circular-oriented electric field can be provided by interlacing electrodes for positive and negative charge, as shown in figure 12, around the media area.
Mass flow induced by osmotic force is another choice, as shown in figure 13. Osmotic force is generated when there is a density difference between any two areas in one solution. The solvent would tend to flow toward the area of the higher solute density. Some people had invented a method to use this phenomenon. In their devices, although very similar to the above example about electrolyte case, they used dielectric fluid as the media, and they used strongly charged electrodes to provide free electrons moving between electrodes such that the electrons would ionize some molecules of the dielectric fluid. The molecule ions tended to move to negatively charged electrode and created the density difference required for the generation of the osmotic force. This kind of actuation is also named ion-drag actuator.
When the media is a solid material, a torque can be generated between the stator and the rotor by periodically generating the deformation in the media material. Imagine how some caterpillars move without walking by foot. They typically bend and stretch their bodies periodically, such that they can receive movement by means of frictions between their skins and the sticks on trees. The nanomotor can work in the same way. Like the electrolyte example above, a circular-oriented "bend and stretch" structure can be made to generate torque about the shaft. In this case, the media material can be only connected to the rotor, only connected to the stator, or connected to none of them. An example is shown in figures 14a and 14b, where figure 14b is a detailed view of the rotor and the electrode.
The term "periodical" implies vibration. The structure is not necessarily in the "caterpillar" form, but a disk-shaped material can be used that can be vibrated like a Pizza turning on the cooker's fingertip. Just like a cell phone ringing in vibration mode, it moves or even rotates on the table. Generally, periodical deformation (or vibration) and friction can generate movement, and the rotation motion we need is a special case of the movement. There are several ways the deformation in the material can be achieved. The first is adjusting temperature to change the atomic lattice structure, named "phase", of the material. Shape memory alloy (SMA) is a good example. Decades of degree's temperature raise can make a properly designed SMA structure generating a big geometrical change.
The second one is thermal expansion or contraction, which is a similar concept like that of the first one, as shown in figure 15. The third, in addition to heat energy, electric field can be used to contract a dielectric media material to generate deformation, such as bending. Finally, electric voltage can be directly applied to the media when piezoelectric material is used as the media material. Piezoelectric material can generate high deformation and high force and is widely applied in ultrasonic motors, in which an electric wave of high frequency is used to actuate a piezoelectric structure disposed between the rotor and the stator (In most cases, the rotor itself is the piezoelectric structure) . See figure 16a and 16b, where figure 16b is a detailed view of the rotor and the electrodes .
In most cases, the rotor is combined with the media structure. The rotor has teeth formed around it. For instance, in a triangular shape, which allows the rotor to slide along the slope of the hypotamous in one direction but not move back against the vertical edge. The stator is further comprised of a plurality of electrodes surrounding the rotor without contact. In operation, the electrodes are charged interchangingly, such to generate induced charge on the teeth of the rotor. The attracting force between the teeth and the electrodes then generates a torque.
(1) GI tract. Colonoscopy and Endoscopy both currently can only exam the surface of the GI tract. When suspicious areas that may represent cancer are identified, a biopsy is required. OCT has the advantage of visualizing 2 - 4 mm into the wall of the GI tract and has resolution to the level of a single cell. The probe can provide histologic images without the need to biopsy tissue to visualize and diagnose cancer in real time.
(3) Cervical and uterine cancer. Currently the gold standard for diagnosing cervical cancer is a pap smear, where cells are scraped off the cervix, and examined under a light microscope to diagnoses cancer. Similarly, women also have the inner lining of the uterus scraped and examined under a microscope to identify cancer cells. The probe 100 can image dysplastic and malignant lesions and quantify changes in the nucleous .
1. A catheter imaging probe for a patient comprising:
a conduit through which energy is transmitted;
a first portion through which the conduit extends; and
a second portion which provides movement relative to the conduit to redirect the energy from the conduit.
2. A probe as described in Claim 1 wherein the first portion includes an inlet tube through which fluid flows and wherein the second portion is moved by flowing fluid from the inlet tube.
3. A probe as described in Claim 2 wherein the second portion includes a rotor through which the conduit extends and a capsule containing the rotor, the rotor and inner surface of the capsule defines at least one flowing route extending about the rotor, guiding the fluid flowing long the flowing route and causing the rotor to rotate about the conduit via reactive force provided by the fluid.
4. A probe as described in Claim 3 wherein the second portion includes a turbine having the rotor and the capsule which is turned by the flowing fluid.
5. A probe as described in Claim 4 wherein the rotor includes a rotating center shaft through which the conduit extends, and spiral shaped inner grooves which extend from the center shaft that provide a rotating torque to the center shaft when the flowing fluid flows against the grooves that causes the center shaft to rotate about the conduit.
6. A probe as described in Claim 5 wherein the second portion has one or more optical redirection elements attached to the center shaft which redirects the energy from the conduit.
7. A probe as described in Claim 6 wherein the conduit is a radiation waveguide.
8. A probe as described in Claim 7 wherein the radiation waveguide is an optical fiber.
9. A probe as described in Claim 8 wherein the optical redirection element includes a prism which reflects light from the conduit, the prism rotating with the center shaft.
10. A probe as described in Claim 9 wherein the turbine includes knobs which support the center shaft which allows the shaft to rotate without wobbling.
11. A probe as described in Claim 10 wherein the first conduit includes at least one outlet tube through which fluid flows from the second portion.
12. A probe as described in Claim 11 wherein the second portion includes a cover having at least a portion which is transparent to the energy which encapsulates the capsule and contacts the first portion so no fluid can escape from the second portion except through the outlet tube.
13. A probe as described in Claim 12 wherein the capsule defines a cylinder attached to the first portion from which the knobs extend and that defines a chamber which fluid from the inlet tube flows through, the turbine is disposed in the chamber.
14. A probe as described in Claim 13 wherein the second portion includes one or more focusing elements which reshape the energy.
15. A probe as described in Claim 14 wherein the focusing element is chosen from the group consisting of a lens, mirror, lens/mirror combination, prism, and liquid crystal.
16. A probe as described in Claim 15 including a fluid source connected to the inlet tube.
17. A probe as described in Claim 16 wherein the fluid source includes a pump which pumps the fluid from the fluid source.
18. A probe as described in Claim 17 wherein the fluid in the fluid source is chosen from the group consisting of nitrogen, helium, C02, saline, water, D5W, lactated ringers or artificial blood.
19. A probe as described in Claim 18 wherein the second portion includes a wart extending from the turbine.
20. A probe as described in Claim 19 wherein the first portion includes a second radiation energy guide aligned to direct energy to the wart that reflects the energy back to the second radiation energy guide only when the tip of the second energy guide is aligned with the wart.
21. A method for imaging a patient comprising the steps of:
inserting a catheter into the patient; and
rotating a second portion of the catheter relative to a conduit extending through a first portion of the catheter, which redirects the energy transmitted through the conduit to the patient and receives the energy reflected back to the second portion from the patient and redirects the reflected energy to the conduit.
22. A method as described in the Claim 21 wherein the rotating step includes the step of flowing fluid through an inlet tube to the second portion to turn the second portion.
23. A method as described in Claim 22 wherein the following step includes the step of flowing fluid through the inlet tube to turn a rotor of the second portion.
24. A method as described in Claim 23 wherein the flowing step includes the step of flowing the fluid against spiral shaped inner grooves which extend from a rotating center shaft of the turbine to create a rotating torque on the center shaft that causes the center shaft to rotate about the conduit that extends through the center shaft.
25. A method as described in Claim 24 wherein the second portion has a reflecting material attached to the center shaft which redirects the energy from the conduit.
26. A method as described in Claim 25 wherein the conduit is a radiation waveguide.
27. A method as described in Claim 26 wherein the a radiation waveguide is an optical fiber.
28. A method as described in Claim 27 wherein the reflecting material includes a prism which reflects light from the conduit, and including the step of rotating the prism with the center shaft as the center shaft is rotated by the flowing fluid.
29. A method as described in Claim 28 wherein the rotating step includes the step of rotating the center shaft that is supported by knobs of a cylinder of a turbine in which the center shaft is disposed.
30. A method as described in Claim 29 wherein the flowing step includes the step of flowing the fluid from the inlet tube through the chamber of the cylinder.
31. A method as described in Claim 30 wherein the flowing step includes the step of removing the fluid flowing from the cylinder of the second portion through at least one outlet tube that extends through the first portion.
32. A method as described in Claim 31 wherein the first portion includes a second radiation energy guide aligned to direct energy to the wart that reflects the energy back to the second radiation energy guide only. when the tip of the energy guide is aligned with the wart.
33. A method as described in Claim 32 wherein the angular position of the second portion is monitored by the energy guided by the second radiation energy guide.
34. A method as described in Claim 31 wherein the rotating direction and speed of the second portion are controlled by the pressure difference between the inlet and outlet .
35. A probe as described in Claim 3 wherein the second portion includes a mill having the rotor and the capsule .
36. A probe as described in Claim 35 wherein the rotor includes a wheel.
37. A probe as described in Claim 36 wherein the capsule holds the wheel.
38. A probe as described in Claim 37 wherein the conduit is a radiation wave guide.
39. A probe as described in Claim 38 wherein the radiation wave guide is an optical fiber.
40. A probe as described in Claim 39 wherein the wheel includes a plug, and fins which extend radially from the plug, the fins pushed by the fluid causing the plug to rotate.
41. A probe as described in Claim 40 wherein the capsule includes an inlet port and an outlet port.
42. A probe as described in Claim 41 wherein the second portion has a reflecting material attached to the plug which redirects the energy from the optical fiber.
43. A probe as described in Claim 42 wherein the reflecting material includes a prism which reflects light from the optical fiber, the prism rotating with the plug.
44. A probe as described in Claim 43 wherein the capsule includes a first pocket and a second pocket, in which a first end of the plug and a second end of the plug are respectfully disposed, the first and second pockets maintaining the plug in position in the capsule as the plug rotates .
45. A probe as described in Claim 44 wherein the second portion includes a cover having at least a portion of which is transparent to the energy which encapsulates the capsule and contacts the first portion so no fluid can escape from the second portion except through the outlet tube.
46. A probe as described in Claim 45 including a fluid source connected to the inlet tube.
47. A probe as described in Claim 46 wherein the fluid in the fluid source is chosen from the group consisting of nitrogen, helium, saline, C02, D5W, lactated ringers, water or artificial blood.
48. A method as described in Claim 21 wherein the flowing step includes the step of flowing fluid through the inlet tube to turn a wheel of the rotor of a mill of the second portion.
49. A method as described in Claim 48 wherein the flowing step includes the step of flowing the fluid against fins which extend from a rotating plug of the wheel to cause the wheel to rotate about the conduit that extends through the plug.
50. A method as described in Claim 49 wherein the second portion has a reflecting material attached to the plug which redirects the energy from the conduit.
51. A method as described in Claim 50 wherein the conduit is an optical fiber.
52. A method as described in Claim 51 wherein the reflecting material includes a prism which reflects light from the conduit, and including the step of rotating the prism with the plug as the wheel is rotated by the flowing fluid.
53. A method as described in Claim 52 wherein the rotating step includes the step of rotating the wheel that is disposed in pockets of a capsule of the mill in which the wheel is disposed.
54. A method as described in Claim 53 wherein the flowing step includes the step of flowing the fluid from the inlet tube through an inlet port of the capsule into the capsule .
55. A method as described in Claim 54 wherein the flowing step includes the step of removing the fluid flowing from an outlet port of the capsule of the second portion through at least one outlet tube that extends through the first portion so a rotational flow path is created with the fluid through the capsule which rotates the wheel as the fluid flows against the fins.
56. A method as described in Claim 55 wherein the first portion includes a second radiation energy guide aligned to direct energy to a wart that reflects the energy back to the second radiation energy guide only when the tip of the second energy guide is aligned with the wart.
57. A method as described in Claim 56 wherein the angular position of the second portion is monitored by the radiation energy guided by the second radiation energy guide.
58. A method as described in Claim 55 wherein the rotating direction and speed of the second portion are controlled by pressure difference between the inlet and outlet .
59. A probe as described in Claim 1 wherein the second portion is a nanomotor that includes a nanorotor, a nanostator, and a media structure formed with medium materials, the first portion includes a driving energy line via which driving energy is transmitted to the media structure, whereby the medium structure actuate the second portion by converting the driving energy into a reactive force between the nanostator and the nanorotor, wherein the second portion has a reflecting material attached to the nanorotor, thereby redirecting the energy from the conduit, wherein the conduit is a radiation wave guide.
60. A probe as described in Claim 51 wherein the medium materials are induced by the driving energy with osmotic pressure that provide the reactive force.
61. A probe as described in Claim 52 wherein the medium materials include electrolyte and the driving energy is electricity energy.
62. A probe as described in Claim 51 wherein the medium materials are induced by the driving energy with difference of surface tension that provide the reactive force .
63. A probe as described in Claim 54 wherein the medium materials include water and the driving energy is radiation wave energy that generating heat.
64. A probe as described in Claim 54 wherein the medium materials include water and the driving energy is electricity energy that generating heat.
65. A probe- as described in Claim 51 wherein the medium materials are induced by the driving energy with magnetic field variation that provide the reactive force.
66. A probe as described in Claim 57 wherein the medium materials include conductive coils and the driving energy is electricity energy.
PCT/US2004/012773 2003-04-28 2004-04-23 Catheter imaging probe and method WO2004096049A2 (en)
EP04760378A EP1620013A4 (en) 2003-04-28 2004-04-23 Catheter imaging probe and method
US10/548,982 US20060241493A1 (en) 2003-04-28 2004-04-23 Catheter imaging probe and method
AU2004233872A AU2004233872C1 (en) 2003-04-28 2004-04-23 Catheter imaging probe and method
CA002521144A CA2521144A1 (en) 2003-04-28 2004-04-23 Catheter imaging probe and method
MXPA05011155A MXPA05011155A (en) 2003-04-28 2004-04-23 Catheter imaging probe and method.
JP2006513317A JP2006524553A (en) 2003-04-28 2004-04-23 The catheter imaging probe and methods
US11/567,244 US7844321B2 (en) 2003-04-28 2006-12-06 Rotating catheter probe using a light-drive apparatus
US12/638,927 US8996099B2 (en) 2003-04-28 2009-12-15 Catheter imaging probe and method
US12/902,092 US8401610B2 (en) 2003-04-28 2010-10-11 Rotating catheter probe using a light-drive apparatus
US13/785,262 US9591961B2 (en) 2003-04-28 2013-03-05 Rotating catheter probe using a light-drive apparatus
US14/672,928 US20150265152A1 (en) 2003-04-28 2015-03-30 Catheter imaging probe and method
US10/548,982 A-371-Of-International US20060241493A1 (en) 2003-04-28 2004-04-23 Catheter imaging probe and method
US10/548,982 A-371-Of-International US7711413B2 (en) 2003-04-28 2004-04-23 Catheter imaging probe and method
US11/551,684 Continuation-In-Part US7853316B2 (en) 2003-04-28 2006-10-20 Rotating optical catheter tip for optical coherence tomography
US11/567,244 Continuation-In-Part US7844321B2 (en) 2003-04-28 2006-12-06 Rotating catheter probe using a light-drive apparatus
US12/638,927 Continuation US8996099B2 (en) 2003-04-28 2009-12-15 Catheter imaging probe and method
WO2004096049A2 true WO2004096049A2 (en) 2004-11-11
WO2004096049A3 WO2004096049A3 (en) 2004-12-02
JP2006204922A (en) * 2005-01-26 2006-08-10 Karl Storz Development Corp Illumination system for visibility apparatus for varying visual field direction
WO2007047974A2 (en) 2005-10-20 2007-04-26 Board Of Regents, The University Of Texas System Rotating optical catheter tip for optical coherence tomography
US7983737B2 (en) 2005-05-27 2011-07-19 Board Of Regents, The University Of Texas Systems Optical coherence tomographic detection of cells and compositions
JP5047248B2 (en) * 2009-09-30 2012-10-10 株式会社日立ハイテクノロジーズ Flow cell detector, and a liquid chromatograph
KR101266518B1 (en) 2011-07-15 2013-05-27 서울대학교산학협력단 Capsule Endoscopy
JP2018516147A (en) * 2015-04-16 2018-06-21 ジェンテュイティ・リミテッド・ライアビリティ・カンパニーＧｅｎｔｕｉｔｙ， ＬＬＣ Micro optical probe for neurological
AT270394T (en) * 1999-07-29 2004-07-15 Jonathan B Rosefsky Belt drive method and system
BR HEART J, vol. 53, 1985, pages 363 - 373
See also references of EP1620013A4
TOPOL EJ; RABBAIC R: "Strategies to achieve coronary arterial plaque stabilization", CARDIOVASC RES, vol. 41, 1999, pages 402 - 417
WO2006119416A3 (en) * 2005-05-04 2007-03-08 Fluid Medical Inc Miniature actuator mechanism for intravascular imaging
EP2461180A1 (en) * 2005-05-04 2012-06-06 Volcano Corporation Miniature actuator mechanism for intravascular imaging
WO2007047974A3 (en) * 2005-10-20 2008-01-03 Univ Texas Rotating optical catheter tip for optical coherence tomography
AU2004233872C1 (en) 2009-08-06
US7809428B2 (en) 2010-10-05 Devices for detection and therapy of atheromatous plaque
US7972272B2 (en) 2011-07-05 Electrostatically driven image probe
2005-01-13 DPEN Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed from 20040101)
Ref document number: 2521144
Ref document number: 171248
Ref document number: PA/a/2005/011155
Ref document number: 1020057020380
Ref document number: 20048112853
Ref document number: 2006513317
Ref document number: 2004233872
Ref document number: 2004760378
Ref document number: 10548982
Ref document number: 2006241493