Apparatus and method for medical applications of laser-driven microfluidic pumps

Abstract

To provide an apparatus for medical applications of an LDMP.SOLUTION: An apparatus for cutting tissue includes: a laser-driven photoacoustic microfluid pump (LDMP); a fiber optic element including a first end and a second end, the first end disposed on the LDMP; and a fluid including at least one of water, blood, plasma, and body fluid; where the fiber is disposed in the fluid, and the LDMP is configured to generate a fluidic jet from the fluid and to cut tissue.SELECTED DRAWING: Figure 1C

Description

Technical Field

[0001] This application relates to devices and methods for medical applications of laser-driven microfluidic pumps, particularly to medical applications of laser-driven photoacoustic microfluidic pumps.

[0002] [Cross-reference to related applications] This application claims the benefit and priority of U.S. Provisional Patent Application No. 62 / 852,485, filed on May 24, 2019, the entire content of which is incorporated herein by reference.

Summary of the Invention

Means for Solving the Problems

[0003] The present disclosure relates to devices and methods for medical applications of laser-driven photoacoustic microfluidic pumps. A drug delivery device according to an aspect of the present disclosure is presented. The device includes a laser-driven photoacoustic microfluidic pump (LDMP: laser-driven photoacoustic microfluidic pump), an optical fiber element having a first end and a second end, the first end of which is disposed on the LDMP, and an open-tube capillary having a first end and a second end, the first end of which is disposed on the optical fiber element, and the open-tube capillary is configured to store a drug. The LDMP is configured to generate a directional fluid jet from the drug and transport the drug. In certain aspects of the present disclosure, the LDMP may include a substrate having a first side and a second side, and a layer of photoacoustic material disposed on the first side of the substrate. The photoacoustic material

[0004] In certain aspects of the present disclosure, the LDMP may include a substrate having a first side and a second side, and a layer of photoacoustic material disposed on the first side of the substrate. ​​​​​​​​​​The material layer is configured to generate directional ultrasound in response to a laser beam incident on the layer. The photoacoustic layer may also comprise nanoparticles.

[0005] A tissue cutting device relating to the perspective of this disclosure is presented. The device comprises an LDMP and a first end An optical fiber element comprising a part and a second end, wherein the first end is arranged in the LDMP. It comprises an optical fiber element and a fluid comprising water, blood, plasma and / or body fluids. The fiber may be placed in the fluid. The LDMP is a fluid jet from the fluid. It may be configured to generate a t and cut the tissue.

[0006] In a certain aspect of this disclosure, the LDMP comprises a substrate having a first side and a second side. The substrate may also include a layer of photoacoustic material disposed on the first side. The material layer is configured to generate directional ultrasound in response to a laser beam incident on the layer. The photoacoustic layer may also comprise nanoparticles.

[0007] From the perspective of this disclosure, an LDMP and an optical fiber element having a first end and a second end, A device for power washing out sediment in arteries. The first end is positioned in the LDMP. The second end is configured to be positioned within an artery. The artery is fluid The fluid comprises water, blood, plasma and / or body fluids. The LDMP is the It is configured to generate a fluid jet from a fluid and remove sediment from an artery.

[0008] From the perspective of this disclosure, the LDMP comprises a substrate having a first side and a second side, and The substrate may include a layer of photoacoustic material disposed on the first side. The layer is configured to generate directional ultrasound in response to a laser beam incident on the layer. The photoacoustic layer may also include nanoparticles.

[0009] A method for transporting drugs to an organization is presented from the perspective of this disclosure. The said method is based on LDMP. - Based on the beam hitting it, directional ultrasound is generated, and the photoacoustic layer The photoacoustic layer expands and contracts thermally in response to the laser beam, and the fluid medium The LDMP comprises generating a directed fluid jet in a solid. The LDMP has a first side and A substrate having a second side, and a layer of photoacoustic material disposed on the first side of the substrate, The photoacoustic material layer responds to a laser beam incident on the layer and exhibits directional properties. It is configured to generate sound waves. The photoacoustic layer comprises nanoparticles. The medium is at the first end The LDMP contains a drug stored in an open capillary having a section and a second end. The first end is positioned. The open capillary is configured to store the drug.

[0010] A device for increasing the flow rate from LDMP, relating to the perspective of this disclosure, is presented. The apparatus is an optical fiber element comprising an LDMP and a first end and a second end, The first end is arranged in the LDMP and comprises an optical fiber element and one end of the optical fiber. It comprises a tube into which a part is inserted, and a fluid comprising water, blood, plasma and / or body fluids. The optical fiber element is placed in the fluid. The LDMP is a strong flow that prevents backflow. It is configured to generate body jets.

[0011] A method for precisely manipulating cells relating to the aspects of this disclosure is presented. The method involves using fluid tweezers. Comprising gripping cells using tweezers, said fluidic tweezers comprising a bidirectional LDMP. The method further comprises, in response to a laser beam impinging on a layer of photoacoustic material, said layer of photoacoustic material being thermally expanded and contracted, and generating two directional fluid jets in a medium, comprising. Said medium comprises cells manipulated by said fluidic tweezers.

[0012] In terms of the present disclosure, said bidirectional LDMP comprises an optical fiber having a first end and a second end and a photoacoustic material layer disposed at said second end of said optical fiber, comprising. Said photoacoustic material layer is configured to generate directional ultrasonic waves in response to a laser beam incident on said photoacoustic material layer and said photoacoustic material layer comprises nanoparticles. comprising.

[0013] A method for destroying a cerebral thrombus according to an aspect of the present disclosure is presented. The method comprises generating a directional high-speed flow based on irradiating a laser beam on an LDMP. The method further comprises, in response to said laser beam impinging on said photoacoustic material layer, thermally expanding and contracting said photoacoustic material layer, and generating a directional fluid jet towards the cerebral thrombus within a cerebral blood vessel. comprising. and generating a directional fluid jet towards the cerebral thrombus within a cerebral blood vessel. comprising. comprising.

[0014] In terms of the present disclosure, said LDMP comprises an optical fiber having a first end and a second end, and a photoacoustic material layer disposed at said second end of said optical fiber. Said photoacoustic material layer is configured to generate directional ultrasonic waves in response to a laser beam incident on said photoacoustic material layer. Said photoacoustic material layer comprises nanoparticles. comprising. comprising.

[0015] Further details and perspectives of representative embodiments of this disclosure are described below with reference to the attached figures. It is explained below. [Brief explanation of the drawing]

[0016] A better understanding of the features and benefits of the disclosed technology is possible through examples where the principles of the technology are used. The following detailed description, which specifies an embodiment, and the accompanying figures can be used to obtain the following: It is likely. [Figure 1A] This shows a quartz window into which gold ions have been implanted and a jet emitted from the window, relating to the aspects of this disclosure. [Figure 1B] This shows a quartz window into which gold ions have been implanted and a jet emitted from the window, relating to the aspects of this disclosure. [Figure 1C] This shows a quartz window into which gold ions have been implanted and a jet emitted from the window, relating to the aspects of this disclosure. [Figure 1D-G] This shows a quartz window into which gold ions have been implanted and a jet emitted from the window, relating to the aspects of this disclosure. [Figure 2A-D] This refers to a jet stream pattern produced by a micropump at various laser powers and spot sizes, relating to the perspective of this disclosure. [Figure 3A-F] The following shows a mobile micropump and two micropumps relating to the aspects of this disclosure. [Figure 4A-F] This illustrates the generation of a jet using a single laser pulse, relating to the aspects of this disclosure. [Figure 5A] This exhibits long-term photoacoustic oscillations excited by a single laser pulse, relating to the aspects of this disclosure. [Figure 5B] A schematic diagram of optical acoustic waves and streaming related to the perspective of this disclosure is shown. [Figure 6] This is a typical embodiment of a drug delivery device to an organization, relating to the perspective of this disclosure. [Figure 7] Figure 6 shows the optical fiber element of the apparatus. [Figure 8A] Figure 7 shows the tip of the optical fiber element in the plane. [Figure 8B] Figure 7 shows the tip of the convex surface of the optical fiber element. [Figure 8C] Figure 7 shows the tip of the concave surface of the optical fiber element. [Figure 9A] This is an image of laser streaming from a glass fiber related to the perspective of this disclosure. [Figure 9B] This is an image of laser streaming from a glass fiber related to the perspective of this disclosure. [Figure 9C] This is an image of laser streaming from a glass fiber related to the perspective of this disclosure. [Figure 10A] This is a diagram of a catheter-based fluid pump relating to the aspects of this disclosure. [Figure 10B] This is a diagram of a catheter-based fluid pump relating to the aspects of this disclosure. [Figure 10C] This is a diagram of a catheter-based fluid pump relating to the aspects of this disclosure. [Figure 11] This is a diagram of a grabbing tool relating to the perspective of this disclosure. [Figure 12] This is a diagram of a jetting and cutting tool relating to the perspective of this disclosure. [Figure 13] This is a diagram of a remotely controlled injector relating to the perspective of this disclosure. [Figure 14] This is a diagram of a microfluidic chip relating to the aspects of this disclosure. [Figure 15] This is a diagram of a laser-driven photoacoustic microfluidic pump synthesis cell relating to the perspective of this disclosure.

[0017] Further details and perspectives of various embodiments of this disclosure are described below with reference to the attached figures. It will be explained. [Modes for carrying out the invention]

[0018] This disclosure relates to apparatus and methods for medical applications of LDMP.

[0019] This disclosure describes specific embodiments, but without departing from the spirit of this disclosure, The fact that various modifications, reorganizations, and substitutions can be made is easily apparent to those skilled in the art. It should be clear that the scope of this disclosure is defined by the claims attached herein. It can be done.

[0020] To facilitate understanding of the principles of this disclosure, refer to the representative embodiments shown in the drawings. Certain terminology is used to describe one thing. Nevertheless, the scope of this disclosure It should be understood that the limitations described herein are not intended to be so. Any changes and further modifications to the features, and any further modifications to the principles of this disclosure as set forth herein, are permitted. Additional applications may be conceivable by those skilled in the art in the relevant technical fields and by holders of this disclosure. This shall be deemed to be within the scope of this disclosure.

[0021] The process of converting (or transforming) one form of energy into another is often This is called transduction. A transducer is used to perform this function. Transductors are commonly used devices, and they transmit physical systems (e.g., pressure, temperature, sound waves). Others are characterized by the direction in which they pass. For example, a sensor is a physical system (e.g., It responds to signals / stimuli (temperature, etc.) and receives electrical signals that represent information about the physical system. It is a type of transducer that generates. On the other hand, an actuator is a physical system (for example) For example, a transducer controls / generates sound waves in response to some kind of electrical signal. The speaker then transforms the electrical signals of the recording into mechanical sound waves.

[0022] As mentioned above, one form of energy can be transformed into another form of energy. These forms of energy include, for example, mechanical energy, electrical energy, and chemical energy. It may also possess energy, electromagnetic energy, thermal energy, and acoustic energy. Light energy ( For example, transforming high-energy photons into mechanical energy, or other energies Research is being conducted on morphological transformation. This involves converting light energy into some form of mechanical energy. To achieve this, efficient momentum transfer is necessary, but achieving this is difficult. Such deformation An efficient system capable of performing this task is desired.

[0023] Micropumps are divided into two groups based on their operating principle: mechanical and non-mechanical. Mechanical micropumps were developed in the 1980s with the advent of micro-electromechanical systems. It was developed in [year] and consists of movable parts such as valves and membranes, and is a giant that directly moves fluid. It is a miniaturized version of a visual pump. Non-mechanical micropumps have no moving parts, but flow Carefully manufactured to generate thermal, electrical, magnetic or acoustic stimuli to move the body A microstructure and electrical contacts are required. The performance of micropumps will improve with advancements in manufacturing technology. Although improvements have been made, the principle and design of micropumps have remained largely the same for the past several decades. In this embodiment, the micropump has no moving parts or electrodes, so it can be used for microfabrication or No nanofabrication is required. The size, number, position, and timing of the micropumps are determined by the rear It may be remotely controlled, reconfigured, and programmed in real time. The pump is made of translucent plastic. It may be equipped with a monic quartz window. The pump is based on the principle of photoacoustic laser streaming. It may be attached, and the ultrasound generated by the resonant laser pulse is acoustic streaming This moves the fluid. The entire surface of the quartz window may be covered with a plasmonic layer. Sound waves can be generated from any position in the window, acting as a launching pad for the micropump.

[0024] Referring to Figures 1A-D, we see a quartz window 100 into which Au ions are implanted, and the ions emitted from that window. The jet is shown. Figure 1A shows the ultraviolet-induced jet of a quartz window 100 into which Au ions have been implanted. The visible absorption spectrum is shown.

[0025] The photoacoustic launcher emits Au ions at approximately 60 keV into a quartz window 100 with a thickness of 0.5 mm. Approximately 6 x 10 cm per square centimeter 16 The amount may be formed by Au ion implantation. Based on the accelerating voltage, Au ions will be implanted within approximately 50 nm of the surface. A relatively large amount is used to obtain a sufficient concentration of Au nanoparticles and corresponding light absorption. It is also possible. Figure 1A shows a quartz window 10 with an injection area 102 placed in the center of the quartz window 100. A schematic diagram of 0 is shown. The absorption spectrum in Figure 1A shows the surface plasmons of Au clusters and nanoparticles. It shows a peak absorption of 103 around 530 nm due to chromatic resonance.

[0026] Figures 1B and 1C show the different angles between the excitation laser beam and the quartz window into which the Au ions are implanted. This shows the setup for generating a jet in degrees.

[0027] A hydrophone is a microphone used to record or listen to underwater sounds. Most hydrophones use piezoelectric transformers to generate an electric potential when subjected to pressure changes such as sound waves. It is based on Deuce.

[0028] To use the window as a launching pad for a micropump, for example, cuvette 106 is Au It may be filled with deionized water 108 that does not contain nanoparticles. The quartz 100 has an adjustable tilt. Installed in a cuvette 106 with an angled surface (for example, a glass cuvette measuring 1 cm on each side) It may also be used. Pulsed laser 104 (for example, 527 nm with a pulse width of 150 ns) The pulsed laser is focused onto a quartz window 100 instead of the cuvette wall (at a focal point of 10-cm). (A distance lens) may be used to generate photoacoustic waves 107 and photoacoustic jets. Water 108 To capture the movement with the high-speed color camera 150, red fluorescent polymer microspheres 10⁹ and a laser (for example, a 633-nm HeNe laser) may be used. Wave 107 is detected by hydrophone 120 and subsequently by a high-speed oscilloscope. It may be amplified by a preamplifier before being recorded. For flow imaging A long-pass filter may be used to block 527 nm light. The repetition frequency can be approximately 1000 Hz. Laser pulses are incident from any position on the window. Once the jet is generated, the micropump is ready to operate.

[0029] Figure 1D-G shows the snuff of the jet at incidence angles of 0°, 30°, 40°, and 50°. This shows a shot. The dashed line indicates the window surface 100a in contact with water. Lateral direction The light ray 170 is used to induce fluorescence from microspheres under excitation with green light of approximately 527 nm. This is laser light emitted from the quartz window 100 (Figure 1B) by this micropump. The jet, regardless of the direction of the laser beam, always flows perpendicular to the window surface. From the observations, a simple conclusion is that the jet is driven by momentum transfer from the incident photons. This means that it is not being done. Laser-induced heating of the quartz layer into which Au is injected and The subsequent photothermal expansion does not depend on the angle of incidence of the laser, so the jet is directed perpendicular to the surface. The observation is consistent with the mechanism of photoacoustic streaming and is not inconsistent with previous observations. On the other hand, this window-jet relationship means that the micropump takes into account the direction of the laser beam. This allows the fluid to be pumped in the same direction. The direction of pumping is window 100. It can be changed depending on the direction (Figure 1B).

[0030] Referring to Figures 2A-D, MicroPons under different laser power and spot sizes The jet stream pattern produced by the laser spot is shown. Figures 2A-C show the laser spot. The size is 50 μm in diameter, and the laser power is (A) 6.3 mW, (B) 10 mW, (C) 4 This shows the case of 0mW. Figure 2D shows the case where the laser power is 330mW and the spot size is approximately 300 The example shown is for a size of μm × 50 μm.

[0031] There is a threshold for laser power required to generate a jet. This is shown in Figures 2A-C. This was confirmed by observations. Streaming was not observed at the low power of 6.3mW. However, significant streaming was observed at 10mW power, and even stronger at 40mW. Yes. Firstly, from Figures 2B and 2C, it can be seen that the jet speed is a factor. Speed A fast jet starts with a small initial diameter, and the divergence decreases as it moves forward. Yes. Secondly, as shown by the broad yellow fluorescence path in Figure 2D, a large laser Using a spot or micropump results in less divergence and better collimation at a distance. It is possible to create a jet, but the initial jet size remains small as shown in Figure 2C. These observations relate to the streamlining of the jet, as well as the conservation of mass and inertia of the fluid. This can be roughly understood from the interaction between the and acoustic radiation forces. A high-speed jet from the window Once launched, water must be supplied from the surrounding area, so the jet is ray It originates from the center of the spot, and its initial size is much smaller than the laser spot. Yes. Once the jet leaves the window, its movement is governed by the inertia of the fluid and acoustic radiation forces. The larger the laser spot, the more parallel the ultrasound waves are, resulting in less divergence in the flow. Yes.

[0032] Referring to Figures 3A-C, if the laser beam is moving downwards at a speed of approximately 1 mm / s Snapshots of the stream from 0, 1, and 2 seconds later are shown. The arrows on the sides indicate the end. The position of the laser spot is shown, and the vertical arrow indicates the direction of the laser spot's velocity. Figure 3D -F indicates streaming using two laser beams with different upper and lower laser powers.

[0033] Instantaneous operation of micropumps without the preparation of photoacoustic cavities offers unprecedented freedom. This makes it possible to create micropump patterns and various fluid movements. For example, By sweeping a laser beam, a sweep micropump can be created (Figure 3A- C) Due to the inertia of the fluid, a moving jet cannot travel as far as a stable jet. To generate two micropumps / jets simultaneously, split the beam into two. (See diagram) 3D-F generates two jets using two beams, and the intensity of each jet... This shows that the beam can be controlled independently by each beam. However, the two jets Because they are in close proximity, if both jets are of equal strength, they will merge into a wider jet (Figure 3E). Alternatively, as shown in Figures 3D and 3F, a weaker jet may be swallowed up by a stronger jet. If we consider each jet as a single fountain, then by simply playing with laser beams, all kinds A fountain of the sort can be created, like a dancing waterfall.

[0034] Referring to Figures 4A-F, the generation of a jet by a single laser pulse is shown. The long-pass filter has been removed so that the green light from the laser pulse can also be observed. (Figures 4A, 4B, 4E, 4F). Time-series snapshots of fluid motion before and after laser pulses. Shot. For example, the exposure time is approximately 10 mS. Arrow 403 in Figure 4B indicates quartz plate The image shows the focused spot of the laser on the surface. The bright white color of the microspheres indicates strong fluorescence. This is due to sex and CC saturation (Figures 4C and 4D). Enlarged image of the area indicated by frames A and B. Laser pulse energy: 0.5 m J.

[0035] On-demand jet generation and controlled laser pulse generation are further enhanced by one By examining the laser pulse jet, it becomes possible to investigate the pumping mechanism. Figure 4 shows high-speed images of the fluid every 20ms before and after the laser pulse strikes it. This shows the Kens effect. From Figure 4A, it can be seen that the fluid is almost stationary at first. Laser pulse The fluid only begins to move when it reaches a certain point, as indicated by the green color of some of the tracing particles in Figure 4B. This is indicated by the fact that... Unlike the other water, the water near the window remains still. As shown by the green frame in Figure 4B, The region with high fluid velocity is approximately 1 mm away from the window. Figures 4E and 4F further show 4 After 0 mS, the fluid velocity decreases rapidly and becomes very small.

[0036] In addition to steady-state streamlining and average flow velocity, detailed examination of the trajectory of tracing particles. This provides more information about the local instantaneous velocity of the particle along its trajectory. This means that the camera continuously records the position of the grains during the 10ms exposure time for each image. This is because the fluorescence intensity of a pixel is proportional to the time the particle remained in one position. For stationary particles, the fluorescence intensity of a pixel is such that it creates a bright spot in the image. It appears as a trace. For fast-moving particles, the trace becomes dark due to the short exposure time. However, with slow-moving particles, the trace is longer due to the increasing exposure time for each pixel. It appears brighter. In principle, the total amount of fluorescence or scattered light is the same for the same exposure time, Regardless of whether the particle is moving, the integrated fluorescence intensity obtained from the particle's trajectory is the same. Such correlations can be confirmed by the trajectories in Figures 4A, 4E, and 4F. Tracer particles are It appears bright when it is not moving. In Figures 4E and 4F, the flow is slowing down, The trajectory is dark on the left (starting point) and bright on the right (ending point).

[0037] Refer to Figure 4B, in particular the two trajectories indicated by arrow 402. The trajectories are green spots and bright It starts in red, and the first 1 / 5 of its path (indicated by the tip of arrow 402) is dark. However, it gets stronger after that. These color codes and strength codes are jet This gives a clear picture of the dynamics. The fluid, as revealed by the weak trajectory, It begins to accelerate immediately after being irradiated with a laser pulse, and quickly reaches its maximum speed. After that, it leaves a strong trajectory. As shown, the fluid velocity begins to decrease. When the laser hits the quartz window, the ultrasonic pulses It is generated immediately, but it takes about 0.5 μS to reach the two tracing particles. The time delay is negligible compared to the total exposure time of 10ms. According to theory, the volume force acting on a fluid is proportional to the ultrasonic intensity and in the same direction as the ultrasonic wave propagates. The ultrasound lasts about 0.5 ms, so the fluid is accelerated during this time, and at the end of the ultrasound pulse... It can be assumed that it will reach its maximum speed. Fluid decay begins after the ultrasonic pulse has passed. First, a green laser is visible, followed by a short acceleration period and then a long deceleration period. .

[0038] Referring to Figures 5A and 5B, the mechanism of photoacoustic micropumping is shown. It is a typical long-lasting photoacoustic vibration, excited by a single laser pulse. The pressure converted from the voltage signal of the drawphone is shown on the right axis. The first 30 μS high The drophone signal is shown in Figure 5A. Figure 5B is a schematic diagram of the photoacoustic wave and streaming. This demonstrates that the absorption of the incident laser causes the surface layer to thermally expand and mechanically vibrate. It produces ultrasound. The streamline in Figure 5B is approximately 20 ms after the laser pulse, as shown in Figure 4. It is based on E.

[0039] The mechanism is that Au nanoparticles / clusters are added to the surface of the cuvette cavity. However, this time, except that it is embedded in the surface layer of quartz, it is the same photoacoustic stone as before. This is reaming. Here again, the key to successful laser streaming is a single laser pulse. This allows for the generation of ultrasound that lasts for a long time. Laser-induced heating and implantation The photothermal expansion of the Au particles induces stress within the quartz plate, causing ultrasonic vibrations of the quartz plate. This causes localized surface vibrations and heating, resulting in longitudinal vibrations perpendicular to the quartz surface, and surface It induces two-directional water vibrations of shear vibrations parallel to the plane. However, the shear motion of the plate affects the liquid. Because it decays exponentially throughout the body, it cannot effectively propagate through liquids, and at room temperature... The permeability is usually less than 1 μm. Only the longitudinal vibrations of the quartz plate effectively propagate through the liquid. This vibration induces longitudinal ultrasonic waves in the liquid, and the liquid surface is perpendicular to the plate surface. It brings about a reaction.

[0040] For ion implantation of gold atoms (or other metal atoms) into quartz, glass, or other transparent solid substrates. Therefore, an LDMP is created. The size of the board is small, for example, sub-millimeter size. Alternatively, gold may be poured into a large thin substrate. Then, the thin substrate is made into a small L It may also be diced into DMP.

[0041] The size of the system may also depend on the application. For example, the inside of the stomach For endoscopic surgery, millimeter-sized versions may be used. For applications in the arteries of the heart, sub-sized versions are available. Millimeter-sized lasers may also be used. This small LDMP uses optical fibers to carry the laser to the LDMP. It may be mounted (attached, bonded, or fused) in contact with the bar and generate a fluid jet. The metal atoms are injected directly into the tip of the optical fiber, and the laser travels through the optical fiber to the head. When it reaches its destination, the tip can be used as the head of a fluid jet.

[0042] The fluid may be water, blood, plasma, body fluid, or any other fluid, depending on the medical or surgical application. Other fluids may be provided. The cross-section of the jet is estimated to be less than 0.1 mm in diameter, and the fluid jet Depending on the output of the laser that induces the jet forward, the jet fluid velocity can reach several cm / sec. .

[0043] Referring to Figure 6, a drug delivery device 600 to tissue is shown. This device is LDM P680, optical fiber element 604, and arranged on the optical fiber element 604 or LDMP680 It may also include an open capillary tube 602 and a first end It comprises a portion 604a and a second end portion 604b. The first end portion 604a is connected to the LDMP680. The open capillary 602 may be arranged as follows: first end portion 602a and second end portion 602b The first end portion 602a may be located on the optical fiber element 604. The tubular capillary may be configured to store the drug 608a in the reservoir 608. The DMP680 generates a directional fluid jet from drug 608a, and the drug 608a It may be configured to deliver. The fluid jet may contain gas and / or liquid. However, it is preferably intended to be a liquid.

[0044] The fluid drug is stored in an open-tube capillary 602, one end of which is attached to the LDMP680. The liquid jet containing the drug may be directed towards a target area for transport. Furthermore, before the drug is delivered by the fluid jet, a laser beam is used to create small cavities in the target area. You may pre-drill the holes. If the same laser can be used for drilling and jetting, align the positions. This can be helpful. For example, the size of the target area can be as small as 0.1mm-2mm. It is also possible to scan a larger area with the laser.

[0045] A fluid jet stream can be used as a tool for cutting tissue. A fluid jet stream may puncture a thin film. The bristles may be used to exfoliate a thin layer of tissue membrane. The power may be adjusted to weaken it. LDMP680 is installed. The optical fiber element 604 may be combined with an endoscope set, for example, a fluid jet. By directing the stream towards unwanted tissue, the laser jet targets and cuts cancer cells. It may be used for the purpose of [doing something].

[0046] Fluid jet streams are used to cleanse inflamed tissue before drug delivery. It may be used. A fluid jet stream is a small amount of fluid to relieve the disease of unwanted deposits in the arteries. It may be used as a type of plow. When the optical fiber element 604 is nearly parallel to the artery, The direction of the stream will be at a glancing angle. Filter It is used to filter out small plagues. That's fine.

[0047] The laser can be any wavelength in the range of approximately 180 nm to 1 mm. The fiber may have a diameter ranging from approximately a fraction of a micron to several millimeters or more.

[0048] Fiber-based photoacoustic devices can perform drug delivery or other functions within the human body. For example, using ultrasound via a fiber optic cable to circulate blood and bodily fluids, or to detect tumors in the body. It allows drugs to be moved around. For example, ultrasound can directly target tissues such as kidney stones. It is also possible.

[0049] Referring to Figure 8A-C, the end face 605 of the optical fiber element 604 is a plane 605a, D It may have a simple (concave) shape 605c or a convex shape 605b. For example, convex shape 605 b can be used for laser defocusing. The concave shape 605c is for small target areas. It may be used to focus the laser beam.

[0050] Figures 9A-C illustrate the aspects of laser streaming from glass fiber as described in this disclosure. The image is shown. Figure 9A shows a laser from a gold-injected glass fiber (d=80μm). This demonstrates experimental streaming. On the surface of one end of the glass fiber, at 60 keV, approximately Gold at a rate of 2 × 10¹⁷ / cm² is injected (Figure 9A). 10⁻¹ at a wavelength of 527 nm When a 5mW pulsed (150nm) laser hits the other end, gold-injected glass... Laser streaming occurs from one end of the fiber (Figure 9B). The laser beams into particles inside the glass tube. The child is pushed out (Figure 9C). These types of pumps are non-contact flow pumps, so conventional It can reduce cell damage and thrombosis by mechanically based pumps, very small It is a type of device that drives fluids wherever laser energy can be obtained. It is possible to do so, and / or require electrical or mechanical energy transmission for operation. It has, but is not limited to, many advantages over other mechanical pumps. Provide points.

[0051] Figures 10A-C are diagrams of catheter-based fluid pumps relating to the aspects of this disclosure. The use of laser light as a power source can establish or enhance fluid flow within the body, These enable flexible and small profiling tools. These are "ramjet" engines. It operates similarly to a gin, and the fluid is delivered to a chamber inside a hollow tube, and then the LDMP pump ( For example, it is accelerated by (a single, multiple, and / or multiple parts of the lumen). This process may be modified in multiple ways to improve the effectiveness of the application. Good. For example, by providing a constant flow rate, such a flow rate can be used for laser 1 It is adjusted by the light intensity of 002 (Figure 10A). Pulsating flow simulates the physiological activity of the heart. It can be created to rate. This involves cycling the laser 1002 on or off. This can be achieved by [methods]. In addition, ultrasound or hypersonic fluid circulation can also be used for thrombus removal. It can be created to enhance specific tool activities. For example, multidirectional flow, laser 1 This may be created by adjusting the direction of 002. This depends on the specific application. To enhance the process, it is possible to create a vortex 1005 (Figure 10B). The design of these pumps is optimized for various applications, with various fluid inlets and It is intended that the structure may include an exit and / or a number of windows 1006 (Figure 10C). For example, a method for destroying cerebral thrombi is based on directing a laser beam at the LDMP. The LDMP may also be equipped with the ability to generate directional high-speed flow. The LDMP has a first end and a second end An optical fiber having two ends, and a layer of photoacoustic material disposed at the second end of the optical fiber It is equipped with a device that generates directional ultrasound in response to a laser beam incident on that layer. A layer of photoacoustic material. The layer of photoacoustic material may include nanoparticles. This method is photoacoustic In response to the laser beam striking the layer of material, the layer of photoacoustic material undergoes thermal expansion and contraction. Furthermore, in preparation for generating a directional liquid jet for cerebral thrombosis within the cerebral blood vessels. That's good too.

[0052] Figure 11 is a diagram of the grabbing tool 1100 from the perspective of this disclosure. Catheter 1106 is used when the flow is reversed within the hollow tube 1004. This is also common, and as a result, provides suction capability (e.g., LDMP suction catheter). For example, The grabbing tool 1100 may be used to grasp cells and / or tissues 1110. The Grabbing Tool 1100 is an extremely small and delicate tool that can reach multiple parts of the body. It may be used as a suction tool. Alternatively, the grabbing tool 1100 can be used to remove cells and / Alternatively, it may be used in research on manipulating tissues 1110, or even intracellular elements.

[0053] For example, a grabbing tool can function as a fluid forceps for manipulating cells. This is possible. The fluid tweezers may be equipped with an LDMP, which has a first end and An optical fiber bending unit having a second end and an optical fiber disposed at the second end of the optical fiber It comprises a layer of photoacoustic material. The layer of photoacoustic material is irradiated with a laser beam. It may be configured to generate directional ultrasound in response to the following. The layer of photoacoustic material is It comprises nanoparticles. The photoacoustic material layer responds to a laser beam striking the photoacoustic material layer. A medium that expands and contracts with heat, thereby containing cells manipulated by fluid tweezers. For example, configured to generate two directional fluid jets in a liquid medium. That's good too.

[0054] Figure 12 shows the jetting and / or cutting tool 120 from the perspective of this disclosure. Figure 0. Jetting and / or cutting tool 1200 is generally used for fluids. A flexible hollow tube 1004 configured as a reservoir, and LDMP1204 and , one or more fluid windows 1202 and a pressure valve 120 for generating a high-speed jet flow 1208 It includes 6 and uses fluid accelerated by an LDMP pump ("LDMP jet"). The jetting and / or cutting tool 1200 used is very small in size. Because it is flexible, it would likely be superior to existing "hydrojet" knives. The jetting and / or cutting tool 1200 is used with ambient fluid and / or ch It may also be equipped with the use of fluid within the chamber. Very high flow rates, or oscillating flow At low rates (e.g., high rates and high frequencies), such tools are useful for organizations or It can cut small cellular structures.

[0055] Figure 13 is a diagram of a remotely controlled injector 1300 relating to the aspects of this disclosure. The 1300 type injector is generally equipped with a catheter 1304, and the catheter 1304 Inside are LDMP1302, payload 1306 (e.g., drug), and pressure A pressure valve 1308 configured to regulate force, and a payload ejector 1310. Payload 1306, after being encapsulated, is activated and accumulates in areas or cells of the body. It may be pumped to an extreme degree. The remotely controlled injector 1300 can, for example, dispense certain drugs. In cell therapy, where the transport of the product needs to be carried out in a very small size, or in the body It is used in activities such as in vitro fertilization or gene therapy where small amounts of material may be injected into cells. It may be used.

[0056] Figure 14 is a diagram of the microfluidic chip 1400 as relating to the aspects of this disclosure. Body tip 1400 is an LDMP mixer 1404 for mixing two or more fluids. A corresponding mixing chamber 1402 may be provided. Microfluidics is a scientific research institute. It may be used in research and drug development. The LDMP pump 1406 can be used, for example, to transport a catheter. Through (a) or directly embedded in the circuit, the movement of fluid within a microfluidic circuit. It may be produced. The mixing chamber is used to facilitate the chemical reaction. This can be done, and mixing is induced by the fluid flow induced by LDMP (c ).

[0057] Figure 15 shows LDMP-synthesizing cell 1502 as described in this disclosure. Gold particles 1506 By embedding it in the lipid structure of the cell, the external laser 1504 can be used to target these cells 1502 It can be used to move and operate it.

[0058] The embodiments disclosed herein are examples of the disclosure and can be embodied in various forms. This is also fine. For example, certain embodiments described herein are described as separate embodiments. Each embodiment of this specification may be combined with one or more other embodiments of this specification. Certain structural and functional details disclosed herein shall be construed as limited in scope. It should not be the basis for the claims, and any appropriately detailed structure This disclosure is interpreted as representative grounds for instructing those skilled in the art to adopt various approaches in this context. It should be. Similar reference numbers refer to similar or identical elements throughout the description of the figure. Sometimes.

[0059] "In one embodiment," "In an embodiment," "In various embodiments," The phrases "in some embodiments" or "in other embodiments" are... Each of these may refer to one or more identical or different embodiments relating to this disclosure. A or B The phrase in the form of "(A), (B), or (A and B)" means "(A), B, or A phrase of the form "(A);(B);(C);(A This means "and B); (A and C); (B and C); or (A, B, and C)".

[0060] Any of the methods, programs, algorithms, or codes described herein are prohibited. It can be converted or expressed in a programming language or computer program. The terms "programming language" and "computer program" as used in this document Each of them is equipped with all the languages ​​used to specify instructions to the computer, and The following languages ​​and their derivatives are included (but are not limited to): Assembler, BASIC, batch files, BCPL, C, C+, C++, Delphi, Fortnite an, Java, JavaScript, machine code, OS command language (opera tion system command language), Pascal, Per PL1, a scripting language, Visual Basic, is itself a program. Metalanguages, 1st generation, 2nd generation, 3rd generation, 4th generation, 5th generation, or later generations All computer languages. Also, databases and other data schemas, and any other. It also includes a metalanguage. Interpreter type, compiled type, or compiled type and interpreter There is no distinction between languages ​​that use both compiled and programmed approaches. There is no distinction between source and compilation versions. Therefore, the programming language has multiple states (source, compilation). If a reference to a program exists in such a way (e.g., in an object, link, etc.), then the reference is to such a program. This refers to any and all of the state. References to the program refer to the actual instructions and / or It may include the intent behind that command.

[0061] Please understand that the above explanation is merely illustrative of this disclosure. Deviating from this disclosure is prohibited. However, various alternatives and modifications can be devised by those skilled in the art. Therefore, this disclosure does not address the issue of alternative solutions. It is intended to include all alternatives, modifications, and differences such as those shown. See the attached diagram. The embodiments described herein are presented solely to illustrate specific examples of the present disclosure. Other elements, steps, or methods substantially different from those described in the above and / or attached claims. Laws and technologies are also intended to be within the scope of this disclosure.

Claims

1. A tissue cutting device, A flexible hollow tube having one or more fluid windows, A laser-driven photoacoustic microfluidic pump (LDMP) is disposed inside the hollow tube, An optical fiber element having a first end and a second end, wherein the first end is arranged in the LDMP, A fluid comprising at least one of water, blood, plasma, or body fluid, Equipped with, The optical fiber element is placed in the fluid and configured to direct the laser beam towards the LDMP. The hollow tube is placed in the fluid and is configured as a reservoir for the fluid that is transported into the hollow tube through the fluid window. The LDMP is configured to generate directional ultrasound in response to the laser beam, accelerate the fluid in the hollow tube with the directional ultrasound to generate a fluid jet from the fluid in the hollow tube, and use the fluid jet to cut tissue.

2. The aforementioned LDMP is, A substrate having a first side and a second side, A layer of photoacoustic material disposed on the first side of the substrate, wherein the layer of photoacoustic material is configured to generate directional ultrasonic waves in response to a laser beam incident on the layer of photoacoustic material, and the layer of photoacoustic material comprises nanoparticles. The apparatus according to claim 1, comprising:

3. The apparatus according to claim 1, further comprising a pressure valve located at the end of the hollow tube from which the fluid jet is discharged, in order to increase the velocity of the fluid jet.

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