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WO2001070381A2 - Procede et dispositif de regulation acoustique de solutions liquides dans des dispositifs microfluidiques - Google Patents

Procede et dispositif de regulation acoustique de solutions liquides dans des dispositifs microfluidiques Download PDF

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Publication number
WO2001070381A2
WO2001070381A2 PCT/US2001/009163 US0109163W WO0170381A2 WO 2001070381 A2 WO2001070381 A2 WO 2001070381A2 US 0109163 W US0109163 W US 0109163W WO 0170381 A2 WO0170381 A2 WO 0170381A2
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Prior art keywords
fluid
acoustic
nucleation
acoustic field
nucleation feature
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Application number
PCT/US2001/009163
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English (en)
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WO2001070381A3 (fr
Inventor
James A. Laugharn, Jr.
Brevard S. Garrison
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Covaris, Inc.
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Filing date
Publication date
Application filed by Covaris, Inc. filed Critical Covaris, Inc.
Priority to CA002402985A priority Critical patent/CA2402985A1/fr
Priority to AU2001250929A priority patent/AU2001250929A1/en
Publication of WO2001070381A2 publication Critical patent/WO2001070381A2/fr
Publication of WO2001070381A3 publication Critical patent/WO2001070381A3/fr

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    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip
    • B01L3/50273—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip characterised by the means or forces applied to move the fluids
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F31/00—Mixers with shaking, oscillating, or vibrating mechanisms
    • B01F31/80—Mixing by means of high-frequency vibrations above one kHz, e.g. ultrasonic vibrations
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F33/00—Other mixers; Mixing plants; Combinations of mixers
    • B01F33/05—Mixers using radiation, e.g. magnetic fields or microwaves to mix the material
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F33/00—Other mixers; Mixing plants; Combinations of mixers
    • B01F33/30—Micromixers
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F33/00—Other mixers; Mixing plants; Combinations of mixers
    • B01F33/40—Mixers using gas or liquid agitation, e.g. with air supply tubes
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F35/00—Accessories for mixers; Auxiliary operations or auxiliary devices; Parts or details of general application
    • B01F35/20—Measuring; Control or regulation
    • B01F35/21—Measuring
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F35/00—Accessories for mixers; Auxiliary operations or auxiliary devices; Parts or details of general application
    • B01F35/20—Measuring; Control or regulation
    • B01F35/22—Control or regulation
    • B01F35/2201—Control or regulation characterised by the type of control technique used
    • B01F35/2202—Controlling the mixing process by feed-back, i.e. a measured parameter of the mixture is measured, compared with the set-value and the feed values are corrected
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F35/00—Accessories for mixers; Auxiliary operations or auxiliary devices; Parts or details of general application
    • B01F35/71—Feed mechanisms
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F35/00—Accessories for mixers; Auxiliary operations or auxiliary devices; Parts or details of general application
    • B01F35/80—Forming a predetermined ratio of the substances to be mixed
    • B01F35/88—Forming a predetermined ratio of the substances to be mixed by feeding the materials batchwise
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F2101/00—Mixing characterised by the nature of the mixed materials or by the application field
    • B01F2101/23—Mixing of laboratory samples e.g. in preparation of analysing or testing properties of materials
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F2101/00—Mixing characterised by the nature of the mixed materials or by the application field
    • B01F2101/44—Mixing of ingredients for microbiology, enzymology, in vitro culture or genetic manipulation
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F2215/00—Auxiliary or complementary information in relation with mixing
    • B01F2215/04—Technical information in relation with mixing
    • B01F2215/0413—Numerical information
    • B01F2215/0418—Geometrical information
    • B01F2215/0427—Numerical distance values, e.g. separation, position
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F2215/00—Auxiliary or complementary information in relation with mixing
    • B01F2215/04—Technical information in relation with mixing
    • B01F2215/0413—Numerical information
    • B01F2215/0418—Geometrical information
    • B01F2215/0431—Numerical size values, e.g. diameter of a hole or conduit, area, volume, length, width, or ratios thereof
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F2215/00—Auxiliary or complementary information in relation with mixing
    • B01F2215/04—Technical information in relation with mixing
    • B01F2215/0413—Numerical information
    • B01F2215/0436—Operational information
    • B01F2215/045—Numerical flow-rate values
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F2215/00—Auxiliary or complementary information in relation with mixing
    • B01F2215/04—Technical information in relation with mixing
    • B01F2215/0413—Numerical information
    • B01F2215/0436—Operational information
    • B01F2215/0477—Numerical time values
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F23/00—Mixing according to the phases to be mixed, e.g. dispersing or emulsifying
    • B01F23/40—Mixing liquids with liquids; Emulsifying
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01F—MIXING, e.g. DISSOLVING, EMULSIFYING OR DISPERSING
    • B01F35/00—Accessories for mixers; Auxiliary operations or auxiliary devices; Parts or details of general application
    • B01F35/20—Measuring; Control or regulation
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01J—CHEMICAL OR PHYSICAL PROCESSES, e.g. CATALYSIS OR COLLOID CHEMISTRY; THEIR RELEVANT APPARATUS
    • B01J2219/00—Chemical, physical or physico-chemical processes in general; Their relevant apparatus
    • B01J2219/00274—Sequential or parallel reactions; Apparatus and devices for combinatorial chemistry or for making arrays; Chemical library technology
    • B01J2219/00277—Apparatus
    • B01J2219/00279—Features relating to reactor vessels
    • B01J2219/00306—Reactor vessels in a multiple arrangement
    • B01J2219/00313—Reactor vessels in a multiple arrangement the reactor vessels being formed by arrays of wells in blocks
    • B01J2219/00315—Microtiter plates
    • B01J2219/00317—Microwell devices, i.e. having large numbers of wells
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01J—CHEMICAL OR PHYSICAL PROCESSES, e.g. CATALYSIS OR COLLOID CHEMISTRY; THEIR RELEVANT APPARATUS
    • B01J2219/00—Chemical, physical or physico-chemical processes in general; Their relevant apparatus
    • B01J2219/00274—Sequential or parallel reactions; Apparatus and devices for combinatorial chemistry or for making arrays; Chemical library technology
    • B01J2219/00277—Apparatus
    • B01J2219/00479—Means for mixing reactants or products in the reaction vessels
    • B01J2219/00484—Means for mixing reactants or products in the reaction vessels by shaking, vibrating or oscillating of the reaction vessels
    • B01J2219/00486—Means for mixing reactants or products in the reaction vessels by shaking, vibrating or oscillating of the reaction vessels by sonication or ultrasonication
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01J—CHEMICAL OR PHYSICAL PROCESSES, e.g. CATALYSIS OR COLLOID CHEMISTRY; THEIR RELEVANT APPARATUS
    • B01J2219/00—Chemical, physical or physico-chemical processes in general; Their relevant apparatus
    • B01J2219/00274—Sequential or parallel reactions; Apparatus and devices for combinatorial chemistry or for making arrays; Chemical library technology
    • B01J2219/00583—Features relative to the processes being carried out
    • B01J2219/00603—Making arrays on substantially continuous surfaces
    • B01J2219/00659—Two-dimensional arrays
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2400/00—Moving or stopping fluids
    • B01L2400/04—Moving fluids with specific forces or mechanical means
    • B01L2400/0403—Moving fluids with specific forces or mechanical means specific forces
    • B01L2400/0433—Moving fluids with specific forces or mechanical means specific forces vibrational forces
    • C—CHEMISTRY; METALLURGY
    • C40—COMBINATORIAL TECHNOLOGY
    • C40B—COMBINATORIAL CHEMISTRY; LIBRARIES, e.g. CHEMICAL LIBRARIES
    • C40B60/00—Apparatus specially adapted for use in combinatorial chemistry or with libraries
    • C40B60/14—Apparatus specially adapted for use in combinatorial chemistry or with libraries for creating libraries

Definitions

  • the invention generally relates to non-contact mixing. More particularly, in one embodiment, the invention is directed to a device and related methods for non-contact mixing and fluid control.
  • Microfluidic devices including "biochip” arrays, “laboratories on a chip”, ultraminiaturized instruments, and the like, have become widely used in research, development, and testing (including diagnostics). Examples include the study of biological-based processes, such as functional genomics ("DNA microarrays"), proteomics, and the like. Often the underlying principle of these reaction devices is an initial binding event between material on a substrate within the device and material in a solution that is exposed to the substrate. Binding events are often diffusion limited and can be enhanced by mixing. Pre- and post-processing such as washing and elution steps can also benefit from mixing in the device.
  • Procedures not necessarily requiring binding such as electrophoresis and some types of chromatography, are also being implemented on very small devices, often using integrated circuit technology from microelectronics processing. These and other process areas that have been or may be implemented in microfluidic device formats and which may benefit from mixing or enhanced fluid flow include extraction, resuspension, solvation, emulsification, separation, and detection.
  • microfluidic devices typically have internal dimensions less than about 50 millimeters and flow velocities typically less than about 10 millimeters per second. For these devices, the Reynolds Numbers encountered are typically less than about one (1), so that flow is smooth and non-turbulent.
  • acoustic energy may be used to effect mixing by multiple processes, including temperature, cavitation, and acoustic streaming.
  • acoustic-based mixing has been shown to improve antibody detection and reduce incubation times.
  • ultrasonic mixing is performed with a nonfocused transducer operating in the 20,000 to 40,000 Hz range. The transducer contacts the sample fluid directly, which severely limits practical applications, particularly with microfluidic devices.
  • cavitation bubbles formed in older devices collapse the bubble nucleation, growth and collapse is not directed, nor controlled device.
  • the invention provides a new apparatus that improves processes related to microfluidic devices and similar structures, including biochips, lab-on-a-chip devices, and multi-well plate formats.
  • the invention also provides for treatment of other internal spaces of microfabricated devices having cavitation promoting features or textures.
  • the apparatus of the invention controls fluid flow by providing nucleation features at particular locations to lower a cavitation threshold.
  • the apparatus of the invention controls an acoustic field to reduce the cavitation threshold at pre-existing cavitation features.
  • the invention may control the acoustic field, for example, through focussing, blocking, and/or reflecting techniques.
  • the invention provides an apparatus and related methods for its use in mixing and fluid movement control.
  • the apparatus includes an acoustic energy source, such as an ultrasound transducer; a controller for providing a waveform type and amplitude controlling signal to the transducer; and one or more nucleation promoting features.
  • the nucleation features may be, for example, mechanical, electrical or chemical in nature.
  • the apparatus may incorporate feedback control mechanisms for adjusting characteristics of the acoustic field generated by the acoustic source.
  • the volume of fluid mixed or controlled is between about 1 pico liter
  • the volume of fluid is between about 10 nanoliters (nl) to about 100 nl
  • the acoustic source/transducer, the controller and the nucleation promoting features are fabricated integrally with a microdevice containing a fluid to be mixed or caused to flow.
  • one or both of the acoustic source and the controller are fabricated separately from and located remotely to the microdevice.
  • the acoustic source couples to the microdevice, for example, by way of a liquid, gel solid, vapor or gas.
  • the acoustic source may be in contact with the fluid to be controlled.
  • a portion of a microdevice, such as a wall or other structure is the couplant that couples acoustic energy from an acoustic source to the fluid to be controlled.
  • the acoustic energy source may be any suitable source, such as a piezoelectric acoustic source.
  • the source may or may not be focussed.
  • Source frequencies in the range of about 10 kilohertz (kHz) to about 100 megahertz (MHz) are preferred in the practice of the invention, because at these frequencies, the acoustic field may be usefully focussed or otherwise shaped and controlled.
  • the resulting focal zone in the microdevice can be small.
  • the size of the focal zone varies approximately inverse to the frequency. By way of example, at about 3 MHz, focal zones of about 1 mm in diameter and about 4 mm long can be obtained.
  • the diameter can be less than about 0.3 mm and the length about 2 mm.
  • Non-focussed transducers operating at these frequencies may have useful natural focussing.
  • a non-focussed transducer 25 mm in diameter operating at 1 MHz will produce an acoustic beam having a natural focal zone about 7 mm in diameter at its narrowest point.
  • These sizes may be large relative to the regions of interest in microfabricated devices.
  • the ultrasonic energy delivered is sufficiently intense to at least form a cavitation bubble in a target zone.
  • the ultrasonic energy delivered is sufficiently intense to oscillate the bubble in the target zone. At still higher energies the delivered ultrasonic energy can result in formation and streaming of bubble(s) in the target zone; this is preferred for some types of microfluidic devices.
  • a piezoelectric acoustic transducer is integrally formed in a microfabricated device
  • an array of piezoelectric acoustic drivers are co-fabricated with an array of active sites adapted, for example, for detection or reaction.
  • An example of a suitable piezoelectric acoustic source is provided in the fabrication of atomic force microscopes and similar devices.
  • the acoustic source is movable with respect to the target microdevice components.
  • the target microdevice is moveable with respect to the acoustic source.
  • the invention provides an individual pathway from the acoustic source to each element of an array in the microdevice containing the fluid to be controlled. According to one embodiment, this is accomplished by providing an acoustic waveguide to conduct acoustic energy to each element of the array of the microdevice.
  • a sound conducting material such as water, vapor, gas, gel, or solid material, can be placed between the acoustic source and the microdevice.
  • a water bath may be employed to conduct acoustic energy from the acoustic source of the mixing apparatus to a microdevice containing the liquid to be mixed.
  • nucleation sites are positioned at specific locations.
  • the ultrasonic energy is directed to a region containing nucleation sites.
  • the nucleation sites are features or textures that act to promote the formation of bubbles and gas cavities within a fluid.
  • the features may be point features such as pits, crevices, defects or linear features such as scratches, grooves or ridges, or arrays of point features or linear features.
  • the features may also be embodied in variations in hydrophobicity, wetability, surface energy and/or a distribution of impurities or contaminants on or in a surface of the microdevice. Multiple features may be employed in regular arrays or randomly in a region to create cavitation inducing textures within a microdevice.
  • the features are disposed at locations on or within a fluid device such that desired mixing or flow patterns are achieved in the presence of an appropriate acoustic field.
  • the nucleation sites may also be disposed in the liquid to be controlled. Such nucleation sites can be, for example, a particle, bead, microsphere of resin.
  • Localized variations in material properties such as acoustic impedance, hydrophobicity, wetability, or surface energy may be employed as nucleation sites to create cavitation inducing loci on a surface of the microdevice and may be beneficially combined with the above discussed nucleation sites.
  • a distribution of impurities in or on a surface of the microdevice may also be employed as nucleation-promoting features.
  • electrodes can be employed to facilitate nucleation at particular sites.
  • the invention directs acoustic energy to commonly occurring irregularities, which may be created in the construction of fabricated fluid devices, such as rough cut edges, to nucleate bubbles at predictable, reliable locations.
  • cavitation effects may be used to induce rotational or convective flow within a fluid in a microdevice chamber, causing local mixing.
  • cavitation effects may be used to induce bubble formation and decay within a defined portion of a fluid conduit, thereby inducing a localized valve effect.
  • bubbles or cavities are generated and released from a nucleation locus or loci such that they stream in response to acoustic field gradients for the purpose of causing fluid flow within a chamber or conduit.
  • the above effects may be applied to a variety of fluids, particularly biochemical fluids, molecules and reactions.
  • the localized acoustic energy may be used for a variety of purposes. Among these are mixing fluids, moving fluids, improving reaction rates, accelerating molecular interactions, conditioning reaction sites, denaturing molecules, and if required, providing local heating.
  • Figure 1 is a schematic illustration of one embodiment of the apparatus according to the invention
  • Figure 2 is a schematic illustration of one example of sonic energy control showing sine waves at a variable amplitude and frequency
  • Figure 3 is a schematic illustration of one example of an intra-sample positioning (dithering) profile showing height, height step, and radius;
  • Figure 4A is a schematic illustration of a vertical-sided treatment vessel
  • Figure 4B is a schematic illustration of a conical treatment vessel
  • Figure 4C is a schematic illustration of a curved treatment vessel
  • Figures 5 A — 5C are schematic illustrations of several embodiments of a treatment vessel with a combination of an upper and lower member and samples in the vessels prior to treatment;
  • Figure 6A is a schematic illustration of a treatment vessel positioned over a collection container prior to transferring the contents of the vessel to the container
  • Figure 6B is a schematic illustration of a treatment vessel positioned over a collection container after transferring some of the contents of the vessel to the container;
  • Figure 7 is a schematic illustration of an embodiment of the invention with a microtiter plate containing samples, such that one of the wells of the microtiter plate is positioned at the focus point of sonic energy;
  • Figure 8 is a conceptual diagram detailing the life cycle of a cavitation bubble formation and collapse, according to an illustrative embodiment of the invention;
  • Figure 9 is a conceptual diagram showing the stages of nucleation and growth of a gas body in a microcavity in a substrate, according to an illustrative embodiment of the invention.
  • Figure 10 is conceptual diagram depicting an acoustic microstreaming-based mixing device according to an illustrative embodiment of the invention.
  • Figure 11 is a conceptual diagram of an exemplary configuration of a cavitation promoter array according to an illustrative embodiment of the invention.
  • Figures 12A and 12B are conceptual diagrams depicting micro flow valve according to an illustrative embodiment of the invention.
  • Figure 13 is a conceptual diagram depicting the directional acceleration of fluid flow according to an illustrative embodiment of the invention;
  • Figures 14A-14D are conceptual diagrams depicting mass transfer across a field of nucleation sites according to an illustrative embodiment of the invention.
  • Figure 15 is a conceptual diagram depicting mixing of fluid on a microscope slide, according to an illustrative embodiment of the invention.
  • Figure 16 is a conceptual diagram depicting electrode cleaning according to an illustrative embodiment of the invention
  • Figure 17 is a conceptual diagram depicting an electrode nucleation feature according to an illustrative embodiment of the invention.
  • Figure 18 is a conceptual diagram of a MEM constructed according to an illustrative embodiment of the invention. Description of an Illustrative Embodiment
  • Acoustic energy as used herein is intended to encompass such terms as sonic energy, acoustic waves, acoustic pulses, ultrasonic energy, ultrasonic waves, ultrasound, shock waves, sound energy, sound waves, sonic pulses, pulses, waves, or any other grammatical form of these terms, as well as any other type of energy that has similar characteristics to acoustic energy.
  • “Focal zone” or “focal point” as used herein means an area where acoustic energy converges and/or impinges on a target, although that area of convergence is not necessarily a single focused point.
  • microplate As used herein, the terms “microplate,” “microtiter plate,” “microwell plate,” and other grammatical forms of these terms can mean a plate that includes one or more wells into which samples may be deposited.
  • “nonlinear acoustics” can mean lack of proportionality between input and output. For example, in our application, as the amplitude applied to the transducer increases, the sinusoidal output loses proportionality such that eventually the peak positive pressure in the acoustic field increases at a higher rate than the peak negative pressure. Also, water becomes nonlinear at high intensities, and in a converging acoustic field, the waves become more disturbed as the intensity increases toward the focal point.
  • Nonlinear acoustic properties of tissue can be useful in diagnostic and therapeutic applications.
  • acoustic streaming means generation of fluid flow by acoustic waves. The effect can be non-linear. Bulk fluid flow of a liquid in the direction of the sound field can be created as a result of momentum absorbed from the acoustic field.
  • acoustic microstreaming means time-independent circulation that occurs only in a small region of the fluid around a source or obstacle for example, an acoustically driven bubble in a sound field.
  • acoustic absorption refers to a characteristic of a material relating to the material's ability to convert acoustic energy into thermal energy.
  • acoustic impedance means a ratio of sound pressure on a surface to sound flux through the surface, the ratio having a reactance and a resistance component.
  • acoustic lens means a system or device for spreading or converging sounds waves.
  • acoustic scattering means irregular and multi-directional reflection and diffraction of sound waves produced by multiple reflecting surfaces, the dimensions of which are small compared to the wavelength, or by certain discontinuities in the medium through which the wave is propagated.
  • cavitation means the nucleation, expansion and decay or collapse of a vacuum space (cavity) or gas/vapor space (bubble) in a fluid as a result of an acoustic pressure field.
  • bubble means a gas body or cavity in a fluid or at a fluid/solid interface having in its interior a vacuum, or a gas or mixture of gasses.
  • couplant means any single material or plurality of materials in an acoustic path for coupling acoustic energy from a source location to another location.
  • a couplant can be a portion of a microdevice, such as a wall of a microdevice, used to couple acoustic energy from an acoustic source to an internal chamber of the microdevice.
  • non-contact refers to an acoustic source not being in mechanical contact with a fluid to be controlled.
  • active site means location of a receptor or sensor of any kind, such as, nucleic acid, nucleic acid probe, protein, antibody, small molecule, tissue sample and nonbiological material.
  • couplant means a material that conducts acoustic energy from a source to another location.
  • the apparatus includes a source of sonic energy, a sensor for monitoring the energy or its effect, and a feedback mechanism coupled with the source of sonic energy to regulate the energy (for example, voltage, frequency, pattern) for transmitting ultrasonic energy to a target
  • Devices for transmission may include detection and feedback circuits to control one or more of losses of energy at boundaries and in transit via reflection, dispersion, diffraction, absorption, dephasing and detuning. For example, these devices can control energy according to known loss patterns, such as beam splitting.
  • Sensors can detect the effects of ultrasonic energy on targets, for example, by measuring electromagnetic emissions, typically in the visible, IR, and UN ranges, optionally as a function of wavelength. These effects include energy dispersion, scattering, absorption, and/or fluorescence emission. Other measurable variables include electrostatic properties such as conductivity, impedance, inductance, and/or the magnetic equivalents of these properties. Measurable parameters also include observation of physical uniformity, pattern analysis, and temporal progression uniformity across an assembly of treatment vessels, such as a microtiter plate.
  • the feedback methodology can include fixed electronic elements, a processor, a computer, and/or a program on a computer.
  • the electronic elements, processor, computer, and/or computer program can in turn control any of a variety of adjustable properties to selectively expose a sample to sonic energy in a given treatment. These properties can include modulation of the ultrasonic beam in response to a detected effect.
  • Modifiable ultrasonic wave variables can include intensity, duty cycle, pulse pattern, and spatial location.
  • Typical input parameters that can trigger an output can include change in level of signal, attainment of critical level, plateauing of effect, and/or rate of change.
  • Typical output actions can include sonic input to sample, such as frequency, intensity, duty cycle; stopping sample movement or sonic energy; and/or moving beam within a sample or to the next sample.
  • Figure 1 depicts an electronically controlled ultrasonic processing apparatus 100 that includes an ultrasound treatment system and associated electronics 200, a positioning system 300 for the sample target 800 being treated, and a control system 400 which controls, generates, and modulates the ultrasound signal and controls the positioning system 300 in a predetermined manner that may or may not include a feedback mechanism.
  • the source of sonic energy 230 and the target 800 being treated for example, a sample, multiple samples, or other device are arranged in a fluid bath 600, such as water, such that the source of sonic energy 230 is oriented towards the target 800.
  • the target 800 may be positioned proximate the surface of the fluid bath 600, above the source of sonic energy 230, all being contained within a sample processing vessel 500.
  • a temperature control unit 610 may be used to control the temperature of the fluid in the fluid bath 610.
  • An overpressure system 900 can control, for example, cavitation, by maintaining a positive pressure on the target 800 and may be adjusted, in a predetermined manner that may or may not include feedback processing, by a target pressure controller 910 that is connected to the control system 400.
  • An ultrasound acoustic field 240 can be generated by the sonic energy source 230, for example, a focused piezoelectric ultrasound transducer, into the fluid bath 600.
  • the sonic energy source 230 can be a 70 mm diameter spherically focused transducer having a focal length of 63 mm, which generates an ellipsoidal focal zone approximately 2 mm in diameter and 6 mm in axial length when operated at a frequency of about 1MHz.
  • the sonic energy source 230 is positioned so that the focal zone is proximate the surface of the fluid bath 600.
  • the sonic energy source 230 can be driven by an alternating voltage electrical signal generated electronically by the control system 400.
  • the positioning system 300 can include at least one motorized linear stage 330 that allows the target to be positioned according to a Cartesian coordinate system.
  • the positioning system 300 may position and move the target 800 relative to the source 230 in three dimensions (x, y, z) and may optionally move either or both of the target 800 and the sonic energy source 230.
  • the positioning system 300 can move target 800 during and as part of the treatment process and between processes, as when multiple samples or devices within the target 800 are to be processed in an automated or high-throughput format.
  • the positioning system 300 may position or move the target 800 in a plane transverse to the focal axis of the sonic energy source 230 (x- and y-axes).
  • the positioning system 300 can position and move the target 800 along the focal axis of the sonic energy source 230 and lift or lower the target 800 from or into the fluid bath 600 (z-axis).
  • the positioning system 300 can also position the sonic energy source 230 and any or all of the sensors 700 in the fluid bath 600 along the focal axis of the sonic energy source 230, if the sensors 700 are not affixed in the water bath 600, as well as lift, lower, or otherwise move the sonic energy source 230.
  • the positioning system 300 also can be used to move other devices and equipment such as detection devices and heat exchange devices from or into the fluid bath 600 (z-axis).
  • the linear stages of the positioning mechanism 330 can be actuated by stepper motors (not shown), which are driven and controlled by electrical signals generated by the control system 400, or other apparatus known to those skilled in the art.
  • the control system 400 can include a computer 410 and a user input/output device or devices 420 such as a keyboard, display, printer, etc.
  • the control system is linked with the ultrasound treatment system 200 to drive the sonic energy source 230, with the positioning system 300 to drive the stepper motors described above, with one or more sensors 700 to detect and measure process conditions and parameters, and with one or more controllers, such as the target pressure controller 910, to alter conditions to which the target 800 is exposed.
  • a fluid bath controller 610 can also be linked with the control system 400 to regulate temperature of the fluid bath 600.
  • the user interface 420 allows an operator to design and specify a process to be performed upon a sample.
  • the ultrasound treatment system 200 can include an arbitrary waveform generator 210 that drives an RF amplifier 220, such that the sonic energy source 230 receives an input.
  • the output signal of the RF amplifier 220 may be conditioned by an impedance matching network and input to the sonic energy source 230.
  • the computer 410 also drives and controls the positioning system 300 through, for example, a commercially available motion control board 310 and stepper motor power amplifier device 320.
  • the control system 400 can generate a variety of useful alternating voltage waveforms to drive the sonic energy source 230.
  • a high power "treatment” interval consisting of about 5 to 1,000 sine waves, for example, at 1.1 MHz
  • a low power "convection mixing” interval consisting of about 1,000 to 1,000,000 sine waves, for example, at the same frequency.
  • "Dead times" or quiescent intervals of about 100 microseconds to 100 milliseconds, for example, may be programmed to occur between the treatment and convection mixing intervals.
  • a combined waveform consisting of concatenated treatment intervals, convection mixing intervals, and dead time intervals may be defined by the operator or selected from a stored set of preprogrammed waveforms. The selected waveform may be repeated a specified number of times to achieve the desired treatment result.
  • Measurable or discernible process attributes such as sample temperature, water bath temperature, intensity of acoustic cavitation, or visible evidence of mixing in the sample processing vessel 500, may be monitored by the control system 400 and employed in feedback loop to modify automatically the treatment waveform during the treatment process.
  • This modification of the treatment waveform may be a proportional change to one or more of the waveform parameters or a substitution of one preprogrammed waveform for another. For instance, if the sample temperature deviates excessively during treatment from a set-point temperature due to absorbed acoustic energy, the control system 400 may proportionally shorten the treatment interval and lengthen the convection mixing interval in response to the error between the actual and target sample temperatures. Or, alternatively, the control system 400 may substitute one predetermined waveform for anotiier.
  • the control system 400 may be programmed to terminate a process when one or more of the sensors 700 signal that the desired process result has been attained.
  • the control system 400 controls and drives the positioning system 300 with the motion control board 310, power amplifier device 320, and motorized stage 330, such that the target 800 can be positioned or moved during treatment relative to the source 230 to selectively expose the target 800 to sonic energy, described more fully below.
  • the sonic energy source 230 for example, an ultrasound transducer or other transducer, produces acoustic waves in the "ultrasonic" frequency range.
  • Ultrasonic waves start at frequencies above those that are audible, typically about 20,000 Hz or 20 kHz, and continue into the region of megahertz (MHz) waves.
  • the speed of sound in water is about 1000 meters per second, and hence the wavelength of a 1000 Hz wave in water is about a meter, typically too long for specific focusing on individual areas less than one centimeter in diameter, although usable in non-focused field situations.
  • the wavelength is about 5 cm, which is effective in relatively small treatment vessels.
  • frequencies may be higher, for example, about 100 kHz, about 1 MHz, or about 10 MHz, with wavelengths, respectively, of approximately 1.0, 0.1, and 0.01 cm.
  • frequencies are typically approximately in the tens of kHz, and for imaging, frequencies are more typically about 1 MHz and up to about 20 MHz.
  • repetition rates of pulses are fairly slow, being measured in the hertz range, but the sharpness of the pulses generated give an effective pulse wavelength, or in this case, pulse rise time, with frequency content up to about 100 to about 300 MHz, or 0.1 - 0.3 gigahertz (GHz).
  • the frequency used in certain embodiments of the invention also will be influenced by the energy absorption characteristics of the sample or of the treatment vessel, for a particular frequency. To the extent that a particular frequency is better absorbed or preferentially absorbed by the sample, it may be preferred.
  • the energy can be delivered in the form of short pulses or as a continuous field for a defined length of time.
  • the pulses can be bundled or regularly spaced.
  • a generally vertically oriented focused ultrasound beam may be generated in several ways.
  • a single-element piezoelectric transducer such as those supplied by Sonic Concepts, oodinville, WA, that can be a 1.1 MHz focused single-element transducer, can have a spherical transmitting surface that is oriented such that the focal axis is vertical.
  • Another embodiment uses a flat unfocused transducer and an acoustic lens to focus the beam.
  • Still another embodiment uses a multi-element transducer such as an annular array in conjunction with focusing electronics to create the focused beam.
  • the annular array potentially can reduce acoustic sidelobes near the focal point by means of electronic apodizing, that is by reducing the acoustic energy intensity, either electronically or mechanically, at the periphery of the transducer. This result can be achieved mechanically by partially blocking the sound around the edges of a transducer or by reducing the power to the outside elements of a multi-element transducer. This reduces sidelobes near the energy focus, and can be useful to reduce heating of the vessel.
  • an array of small transducers can be synchronized to create a converging beam.
  • Still another embodiment combines an unfocused transducer with a focusing acoustic mirror to create the focused beam.
  • This embodiment can be advantageous at lower frequencies when the wavelengths are large relative to the size of the transducer.
  • the axis of the transducer of this embodiment can be horizontal and a shaped acoustic mirror used to reflect the acoustic energy vertically and focus the energy into a converging beam.
  • the focal zone can be small relative to the dimensions of the treatment vessel to avoid heating of the treatment vessel.
  • the focal zone has a radius of approximately 1 mm and the treatment vessel has a radius of at least about 5 mm.
  • Heating of the treatment vessel can be reduced by minimizing acoustic sidelobes near the focal zone.
  • Sidelobes are regions of high acoustic intensity around the focal point formed by constructive interference of consecutive wavefronts.
  • the sidelobes can be reduced by apodizing the transducer either electronically, by operating the outer elements of a multi-element transducer at a lower power, or mechanically, by partially blocking the acoustic waves around the periphery of a single element transducer.
  • Sidelobes may also be reduced by using short bursts, for example in the range of about 3 to about 5 cycles in the treatment protocol.
  • the transducer can be formed of a piezoelectric material, such as a piezoelectric ceramic.
  • the ceramic may be fabricated as a "dome", which tends to focus the energy.
  • One application of such materials is in sound reproduction; however, as used herein, the frequency is generally much higher and the piezoelectric material would be typically overdriven, that is driven by a voltage beyond the linear region of mechanical response to voltage change, to sharpen the pulses.
  • these domes have a longer focal length than that found in lithotriptic systems, for example, about 20 cm versus about 10 cm focal length. Ceramic domes can be damped to prevent ringing. The response is linear if not overdriven. The high-energy focus of one of these domes is typically cigar-shaped.
  • the focal zone is about 6 cm long and about 2 cm in diameter for a 20 cm dome, or about 15 mm long and about 3 mm wide for a 10 cm dome.
  • the peak positive pressure obtained from such systems is about 1 MPa (mega Pascal) to about 10 MPa pressure, or about 150 PSI (pounds per square inch) to about 1500 PSI, depending on the driving voltage.
  • the wavelength, or characteristic rise time multiplied by sound velocity for a shock wave is in the same general size range as a cell, for example about 10 to about 40 micron.
  • This effective wavelength can be varied by selection of the pulse time and amplitude, by the degree of focusing maintained through the interfaces between the source and the material to be treated, and the like.
  • the focused ultrasound beam is oriented vertically in a water tank so that the sample may be placed at or near the free surface.
  • the ultrasound beam creates shock waves at the focal point.
  • a focal zone defined as having an acoustic intensity within about 6dB of the peak acoustic intensity, is formed around the geometric focal point. This focal zone has a diameter of approximately 2 mm and an axial length of about 6 mm.
  • Ceramic domes are adaptable for in vitro applications because of their small size. Also, systems utilizing ceramic domes can be produced at reasonable cost. They also facilitate scanning the sonic beam focus over a volume of liquid, by using microactuators which move a retaining platform to which the sample treatment vessel is attached.
  • Another source of focused pressure waves is an electromagnetic transducer and a parabolic concentrator, as is used in lithotripsy.
  • the excitation tends to be more energetic, with similar or larger focal regions. Strong focal peak negative pressures of about - 16 MPa have been observed. Peak negative pressures of this magnitude provide a source of cavitation bubbles in water, which can be desirable in an extraction process.
  • a commercial ultrasonic driver using a piezoelectric ceramic, which is stimulated by application of fluctuating voltages across its thickness to vibrate and so to produce acoustic waves. These may be of any of a range of frequencies, depending on the size and composition of the driver.
  • Such drivers are used in lithotripsy, for example, as well as in acoustic speakers and in ultrasound diagnostic equipment, although without the control systems as described herein.
  • the acoustic waveform of the transducer has many effects, including: acoustic microstreaming in and near cells due to cavitation, that is flow induced by, for example, collapse of cavitation bubbles; shock waves due to nonlinear characteristics of the fluid bath; shock waves due to cavitation bubbles; thermal effects, which lead to heating of the sample, heating of the sample vessel, and/or convective heat transfer due to acoustic streaming; flow effects, causing deflection of sample material from the focal zone due to shear and acoustic pressure, as well as mixing due to acoustic streaming, that is flow induced by acoustic pressure; and chemical effects.
  • the treatment protocol can be optimized to maximize energy transfer while minimizing thermal effects.
  • the treatment protocol also can effectively mix the contents of the treatment vessel, in the case of a particulate sample suspended in a liquid.
  • Energy transfer into the sample can be controlled by adjusting the parameters of the acoustic wave such as frequency, amplitude, and cycles per burst.
  • Temperature rise in the sample can be controlled by limiting the duty cycle of the treatment and by optimizing heat transfer between the treatment vessel and the water bath.
  • Heat transfer can be enhanced by making the treatment vessel with thin walls, of a relatively highly thermally conductive material, and/or by promoting forced convection by acoustic streaming in the treatment vessel and in the fluid bath in the proximity of the treatment vessel. Monitoring and control of temperature is discussed in more detail below.
  • an example of an effective energy waveform is a high amplitude sine wave of about 1000 cycles followed by a dead time of about 9000 cycles, which is about a 10% duty cycle, at a frequency of about 1.1 MHz.
  • the sine wave electrical input to the transducer typically results in a sine wave acoustic output from the transducer.
  • the focused sine waves converge at the focal point, they can become a series of shock waves due to the nonlinear acoustic properties of the water or other fluid in the bath.
  • This protocol treats the material in the focal zone effectively during the "on" time. As the material is treated, it typically is expelled from the focal zone by acoustic shear and streaming.
  • New material circulates into the focal zone during the "off time.
  • This protocol can be effective, for example, for extracting the cellular contents of ground or particulate leaf tissue, while causing minimal temperature rise in the treatment vessel.
  • Further advantage in disruption and other processes may be gained by creating a high power "treat” interval 10 alternating with a low power "mix” interval 14, as shown schematically in Figure 2. More particularly, in this example, the "treat” interval 10 utilizes a sine wave that has a treatment frequency 18, a treatment cycles-per-burst count 26, and a treatment peak-to-peak amplitude 22.
  • the "mix” interval 14 has a mix frequency 20, a mix cycles-per-burst count 28 and a lower mix peak-to-peak amplitude 24.
  • High power/low power interval treatments can allow multiple operations to be performed, such as altering permeability of components, such as cells, within the sample followed by subsequent mixing of the sample.
  • the treat interval can maximize cavitation and bioeffects, while the mix interval can maximize mixing within the treatment vessel and/or generate minimal heat.
  • Adding a longer, high power "super-mix” interval occasionally to stir up particles that are trapped around the periphery of the treatment vessel can provide further benefits.
  • This "super- mix” interval generates additional heat, so it is programmed to treat infrequently during the process, for example, every few seconds. Additionally, dead times between the mix and treat intervals, during which time substantially no energy is emitted from the sonic energy source, can allow fresh material to circulate into the energy focal zone of the target.
  • the waveform of focused sound waves can be a single shock wave pulse, a series of individual shock wave pulses, a series of shock wave bursts of several cycles each, or a continuous waveform.
  • Incident waveforms can be focused directly by either a single element, such as a focused ceramic piezoelectric ultrasonic transducer, or by an array of elements with their paths converging to a focus.
  • a single element such as a focused ceramic piezoelectric ultrasonic transducer
  • multiple foci can be produced to provide ultrasonic treatment to multiple treatment zones, vessels, or wells.
  • Reflected waveforms can be focused with a parabolic reflector, such as is used in an "electromagnetic" or spark-gap type shock-wave generator. Incident and reflected waveforms can be directed and focused with an ellipsoidal reflector such as is used in an electrohydraulic generator. Waveforms also can be channeled.
  • the waveform of the sound wave typically is selected for the particular material being treated. For example, to enhance cavitation, it can be desirable to increase the peak negative pressure following the peak positive pressure. For other applications, it can be desirable to reduce cavitation but maintain the peak positive pressure. This result can be achieved by performing the process in a pressurized chamber at a slight pressure above ambient. For example, if the waveform generated has a peak negative pressure of about -5 MPa, then the entire chamber may be pressurized to about 10 MPa to eliminate cavitation from occurring during the process. Liquid to be treated can be pressurized on a batch or a continuous basis.
  • shock waves of high intensity and short duration are generated.
  • Shock waves may be generated by any method that is applicable to a small scale. Such methods include spark discharges across a known gap; laser pulses impinging on an absorptive or reflective surface; piezoelectric pulses; electromagnetic shock waves; electrohydraulic shock waves created by electrical discharges in a liquid medium; and chemical explosives.
  • microexplosives in wells in a semiconductor-type chip can be fabricated in which the wells are individually addressable.
  • a magnetostrictive material can be exposed to a magnetic field, and it can expand and/or contract such that the material expansion/contraction creates sonic energy.
  • Continuous sinusoidal sound waves can be generated by any process that is appropriate for focusing on a small scale.
  • ceramic piezoelectric elements may be constructed into dome shapes to focus the sound wave into a point source.
  • two or more shock waves may be combined from the same source, such as piezoelectric elements arranged in mosaic form, or from different sources, such as an electromagnetic source used in combination with a piezoelectric source, to provide a focused shock wave.
  • the shock wave is characterized by a rapid shock front with a positive peak pressure in the range of about 15 MPa, and a negative peak pressure in the range of about negative 5 MPa. This waveform is of about a few microseconds duration, such as about 5 microseconds.
  • cavitation bubbles may form. Cavitation bubble formation also is dependent upon the surrounding medium. For example, glycerol is a cavitation inhibitive medium, whereas liquid water is a cavitation promotive medium. The collapse of cavitation bubbles forms "microjets" and turbulence that impinge on the surrounding material.
  • the waves are applied to the samples either directly, as for example, piezoelectric pulses, or via an intervening medium.
  • This medium can be water or other fluid.
  • An intervening medium also can be a solid, such as a material which is intrinsically solid or a frozen solution. Waves also can be applied through a container, such as a bottle, bag, box, jar, or vial.
  • a focused acoustic pulse is useful.
  • a pulse is emitted from a curved source with an elliptical profile, then the emitted acoustic waves or pulses focus in a small region of maximum intensity.
  • the location of the focus can be calculated or determined readily by experiment.
  • the diameter of the focal zone can be of the same general size as or smaller than the diameter of the treatment vessel. Then, mixing energy can be provided to each well for a repeatable amount of time, providing uniform mixing of each sample.
  • the sample is not only moved into position relative to the transducer initially, but positioned during treatment to insure uniform treatment of the sample, where the sample is kept well suspended during treatment.
  • x and y axes define a plane that is substantially horizontal relative to ground and/or a base of an apparatus of the invention, while the z axis lies in a plane that is substantially vertical relative to the ground and/or the base of an apparatus and perpendicular to the x-y plane.
  • One positioning scheme is termed "dithering,” which entails slightly varying the position of the sample relative to the source which can occur by moving the sample through the focal zone in several ways.
  • the sample can be moved in a circle, or oval, or other arcuate path with a certain radius 30 and moved a certain distance 34 in certain increments or steps 32, as depicted schematically in Figure 3.
  • These movements can vary between treatment cycles or during a particular treatment cycle and have several effects.
  • dithering the sample position sweeps the focal zone through the volume of the sample treatment vessel or device, treating material that is not initially in the focal zone.
  • varying the location of the acoustic focus within the vessel tends to make treatment, and the resulting heating, more uniform within each sample.
  • Certain embodiments include drive electronics and devices for positioning of the sample(s).
  • the positioning sequence, optionally including dithering, and the treatment pulse train are pre-programmed, for example in a computer, and are executed automatically.
  • the driver electronics and positioners can be linked through the control system to sensors so that there is "real time" feedback of sensor data to the control system during treatment in order to adjust the device(s) for positioning the sample and prevent localized heating or cavitation.
  • the drive electronics can include a waveform generator matching network, an RF switch or relay, and a radio frequency (RF) amplifier, for safety shutdown.
  • RF radio frequency
  • the positioning system can include a three axis Cartesian positioning and motion control system to position the sample treatment vessel or an array of sample treatment vessels relative to the ultrasound transducer.
  • the "x" and “y” axes of the Cartesian positioning system allow each sample in an array of samples, such as an industry standard microplate, to be brought into the focal zone for treatment.
  • Alternative configurations may employ a combination of linear and rotary motion control elements to achieve the same capabilities as the three axis Cartesian system.
  • Alternative positioning systems may be constructed of self-contained motor-driven linear or rotary motion elements mounted to each other and to a base plate to achieve two- or three-dimensional motion.
  • stepper motors such as those available from Eastern Air Devices, located in Dover, NH, drive linear motion elements through lead screws to position the sample.
  • the stepper motors are driven and controlled by means of Lab VIEW software controlling a ValueMotion stepper motor control board available from National Instruments, located in Austin, TX.
  • the output signals from the control board are amplified by a nuDrive multi-axis power amplifier interface, also available from National Instruments, to drive the stepper motors.
  • the computer controlled positioning system can be programmed to sequentially move any defined array of multiple samples into alignment with the focal zone of the ultrasound transducer. If temperature rise during treatment is an issue, the samples in a multi-sample array can be partially treated and allowed to cool as the positioning system processes the other samples. This can be repeated until all the samples have been treated fully.
  • the positioning system also can move the sample treatment vessel relative to the focal point during treatment to enhance the treatment or to treat a sample that is large relative to the focal zone.
  • clumps of material around the periphery of the treatment vessel may be broken up advantageously.
  • x-y dithering may prevent a "bubble shield" from forming and blocking cavitation in the sample treatment vessel.
  • the x-y dithering may also enhance treatment of sample suspensions that have a high viscosity or become more viscous during treatment and do not mix well.
  • the sample position may also be dithered vertically in the z-axis.
  • the x-y positioning system can cause the focal zone to traverse the sample in order to treat the entire surface of the sample. This procedure may be combined with optical analysis or other sensors to determine the extent of the treatment to each portion of the sample that is brought into the focal zone.
  • the sample or array of samples can be moved relative to the transducer and the other parts of the apparatus.
  • the transducer is moved while the sample holder remains fixed, relative to the other parts of the apparatus.
  • movement along two of the axes, for example, x and y can be assigned to the sample holder and movement along the third axis, z in this case, can be assigned to the transducer.
  • the three axis positioning system enables automated energy focus adjustment in the z-axis when used in conjunction with a sensor for measuring the ultrasound intensity.
  • a needle hydrophone can be mounted in a fixture on the sample positioning system.
  • the hydrophone can be traversed in three dimensions through the focal region to record the acoustic intensity as a function of position in order to map out the focal zone.
  • a number of positions on a sheet of aluminum foil held in the sample holder can be treated in a sequence of z-axis settings.
  • the foil can then be examined to determine the spot size of the damage at each position.
  • the diameter of the spot corresponds generally to the diameter of the focal zone at that z-axis setting.
  • Other, fully automated embodiments of a focusing system can also be constructed.
  • the three axis positioning system also allows the apparatus to be integrated into a larger laboratory automation scheme.
  • a positioning system with an extended work envelope can transfer microplates or other sample vessels into and out of the apparatus. This allows the apparatus to interact automatically with upstream and downstream processes.
  • D. Sensors Visual Monitoring of the Sample Optical or video detection and analysis can be employed to optimize treatment of the sample. For example, in a suspension of biological tissue, the viscosity of the mixture can increase during treatment due to the diminution of the particles by the treatment and/or by the liberation of macromolecules into the solution.
  • Video analysis of the sample during treatment allows an automated assessment of the mixing caused by the treatment protocol. The protocol may be modified during the treatment to promote greater mixing as a result of this assessment.
  • the video data may be acquired and analyzed by the computer control system that is controlling the treatment process.
  • Other optical measurements such as spectral excitation, absorption, fluorescence, emission, and spectral analysis also can be used to monitor treatment of the sample.
  • a laser beam for example, can be used for alignment and to indicate current sample position.
  • Heating of individual wells can be determined by an infrared temperature-sensing probe, collimated so as to view only the well being treated with the ultrasonic energy.
  • an infrared thermal measuring device can be directed at the top unwetted side of the treatment vessel. This provides a non-contact means of analysis that is not readily achievable in conventional ultrasound treatment configurations.
  • the thermal information can be recorded as a thermal record of the sample temperature profile during treatment.
  • Active temperature monitoring may be used as a feedback mechanism to modify the treatment protocol during the treatment process to keep the sample temperature within specified limits.
  • an infrared sensor directed at the sample treatment vessel may input temperature readings to the computer.
  • the computer in accordance with a controlling program, can produce output directed to the circuit enabling the ultrasonic transducer, which in turn can reduce the high power treatment intervals and increase the low power mixing intervals, for example, if the sample temperature is nearing a specified maximum temperature.
  • Bubbles are effective scatterers of ultrasound.
  • the pulsation mode of a bubble is referred to as monopole source, which is an effective acoustic source.
  • monopole source is an effective acoustic source.
  • the bubble simply scatters the incident acoustic pulse.
  • the response becomes more nonlinear, it also starts to emit signals at higher harmonics.
  • acoustic transducer can be configured to detect these emissions. There is a detectable correlation between the onset of the emissions and cell disruption.
  • Bubbles also scatter light. When bubbles are present, light is scattered. Light can normally be introduced into the system using fiber optic light sources so that cavitation can be detected in real-time, and therefore can be controlled by electronic and computer systems.
  • Bubbles can be photographed. This method typically requires high-speed cameras and high intensity lighting, because the bubbles respond on the time frame of the acoustics. It also requires good optical access to the sample under study. This method can give detailed and accurate data and may be a consideration when designing systems according to the invention. Stroboscopic systems, which take images far less frequently, can often give similar qualitative performance more cheaply and easily than high-speed photography.
  • the ultrasound treatment protocol influences the sample temperature in several ways: the sample absorbs acoustic energy and converts it to heat; the sample treatment vessel absorbs acoustic energy and converts it to heat which, in turn, can heat the sample; and acoustic streaming develops within the sample treatment vessel and the water bath, forcing convective heat transfer between the sample treatment vessel and the water bath. In the case of a relatively cool water bath, this cools the sample.
  • the acoustic waves or pulses can be used to regulate the temperature of the solutions in the treatment vessel.
  • the acoustic energy produces a slow stirring without marked heating.
  • energy is absorbed to induce the stirring, heat is lost rapidly through the sides of the treatment vessel, resulting in a negligible equilibrium temperature increase in the sample.
  • the degree of rise per unit energy input can be influenced and/or controlled by several characteristics, including the degree of heat absorption by the sample or the treatment vessel and the rate of heat transfer from the treatment vessel to the surroundings.
  • the treatment protocol may alternate a high-powered treatment interval, in which the desired effects are obtained, with a low power mixing interval, in which acoustic streaming and convection are achieved without significant heat generation. This convection may be used to promote efficient heat exchange or cooling.
  • the thermal information can also be used to modify or control the treatment to maintain the sample temperature rise below a maximum allowable value.
  • the treatment can be interrupted to allow the sample to cool down.
  • the output of the thermal measurement device or system is entered into the computer control system for recording, display on a control console, and/or control of exposure of the sample to sonic energy through a feedback loop, for example by altering the duty cycle.
  • Temperature rise during ultrasonic continuous wave exposure can be controlled, if required, by refrigeration of a liquid or other sample before, during, or after passage through a zone of sonic energy, if processing in a continuous, flow-through mode.
  • a sample In generally stationary discrete sample processing modes, a sample can be cooled by air, by contact with a liquid bath, or a combination of both air and liquid. The temperature is rapidly equilibrated within the vessel by the stirring action induced by the acoustic waves. As a result, and especially in small vessels or other small fluid samples, the rate of temperature increase and subsequent cooling can be very rapid. The rate of delivery of sonic energy to the material can also be controlled, although that can lengthen processing time.
  • Liquids within the sample can be provided at any temperature compatible with the process.
  • the liquid may be frozen or partially frozen for processing.
  • sample temperature may be varied during the procedure.
  • a temperature is selected at which microdomains of liquid water are able to form shock wave induced cavitation due to bubble formation and collapse, resulting in shear stresses that impinge on surrounding tissues. Indeed, gradually altering the sample temperature can be desirable, as it provides focused domains of liquid water for collection of sonic energy for impingement on the surrounding material.
  • Treatment baths can be relatively simple, and can include a water bath or other fluid bath that is employed to conduct the acoustic waves from the transducer to the sample treatment vessel, where the liquid is temperature controlled.
  • the entire bath is maintained at a specific temperature by means of an external heater or chiller, such as a Neslab RTE-210 chiller available from Neslab Instruments, Inc., located in Newington, NH, and heat exchanger coils immersed in the bath.
  • the sides and bottom of the tank containing the bath may have sufficient insulating properties to allow the bath to be maintained substantially uniformly at a specific temperature.
  • FIG. 7 Another embodiment, such as that depicted in Figure 7, employs an inner tray or sample tank 76 made of an insulating material such as rigid polystyrene foam which is set within a larger water bath 84 in a transducer tank 82.
  • the inner tray 76 has heat-exchanger tubes or other heating or cooling devices within it (not shown) to allow a fluid 78 such as ethylene glycol or propylene glycol in the inner tray 76 to be heated or cooled beyond what may be practical for the fluid 84 such as water in the outer bath in the transducer tank 82.
  • the inner tray 76 has an acoustic window 88 in the bottom.
  • the acoustic window 88 is made of a thin film material having low acoustic absorption and an acoustic impedance similar to water.
  • This inner tray 76 is arranged so that the acoustic window 88 is aligned with a transducer 86 which is outside the tray 76, supported with a support 80 in the water 84.
  • a sample 74 is located within a microtiter plate or other sample treatment vessel 72, within the tray 76 and is subjected to the thermal influence of the inner treatment bath 78.
  • the treatment vessel 70 can be movable relative to the transducer 86 with a positioning system 70. Also, sonic energy focuses on the sample 74 through the acoustic window 88.
  • This arrangement permits the use of separate fluids and substantially independent control of the temperature of the inner 76 and outer treatment baths 84.
  • the smaller volume of the inner tray 76 facilitates the use of antifreeze mixtures, such as a mixture of propylene glycol and water, at temperatures below the freezing temperature of water.
  • antifreeze mixtures such as a mixture of propylene glycol and water
  • This allows the samples 74 to be processed and treated at temperatures below the freezing temperature of water.
  • This embodiment is beneficial for treatment applications requiring that the sample materials 74 be maintained at temperatures near or below the freezing point of water. It allows for the containment of treatment bath fluids 78, such as antifreeze solutions, that may not be compatible with the transducer 86 and other system components. It also allows the transducer 86 to be maintained at a different temperature than the samples 74.
  • This embodiment may also be connected with any of the other components described in Figure 1 and is suitable for use in a system with or without feedback loop control.
  • Sample temperature may be required to remain within a given temperature range during a treatment procedure. Temperature can be monitored remotely by, for example, an infra-red sensor. Temperature probes such as thermocouples may not be particularly well suited for all applications because the sound beam may interact with the thermocouple and generate an artificially high temperature in the vicinity of the probe. Temperature can be monitored by the same computer that controls acoustic waveform. The control responds to an error signal which is the difference between the measured actual temperature of the sample and the target temperature of the sample.
  • the control algorithm can be as a hysteritic bang-bang controller, such as those in kitchen stoves, where, as an output of the control system, the acoustic energy is turned off when the actual temperature exceeds a first target temperature and turned on when the actual temperature falls below a second target temperature that is lower than the first target temperature.
  • More complicated controllers can be implemented. For example, rather than simply turning the acoustic signal on and off, the acoustic signal could continuously be modulated proportionally to the error signal, for example, by varying the amplitude or the duty cycle, to provide finer temperature regulation.
  • an alternative to waiting for the sample to cool below a selected temperature before turning the sonic energy on again is to move on to the next sample. More particularly, some of the samples can be at least partially treated with sonic energy, in a sequence, and then, the system can return to the previously partially treated samples to take a sensor reading to determine if the samples have cooled below the selected temperature and to reinitiate treatment if they have. This procedure treats the samples in an efficient manner and reduces the total treatment time for treating multiple samples. Another alternative is to switch to a predefined "cooling" waveform which promotes convection without adding significant heat to a particular sample, rather than moving on to the next sample and returning to the first sample at a later time.
  • control techniques can be used to ensure a uniform temperature distribution.
  • An array of infra-red sensors can be used to determine the distribution of the temperature inside the sample. If areas of increased temperature relative to the rest of the sample appear, then the transducer can be switched from high power "treatment” mode to low power "mixing" mode. In the low power “mixing” mode, the sample is acoustically stirred until the sample is substantially uniform in temperature. Once temperature uniformity is achieved, the high power "treatment” mode is reinitiated.
  • a control system can monitor temperature and responsively turn the various modes on or off. When controlled by a computer, the intervals during which these modes are used can be very short, for example fractions of a second, thereby not significantly prolonging treatment times. Stepping times between wells, or other sample containers, can also be less than a second with suitable design.
  • Cavitation Control In some applications, it can be preferable to treat the sample with as much energy as possible without causing cavitation. This result can be achieved by suppressing cavitation. Cavitation can be suppressed by pressurizing the treatment vessel above ambient, often known as " overpressure," to the point at which no negative pressure develops during the rarefaction phase of the acoustic wave. This suppression of cavitation is beneficial in applications such as cell transformation where the desired effect is to open cellular membranes while maintaining viable cells. In other applications it may be desirable to enhance cavitation. In these applications, a "negative" overpressure or vacuum can be applied to the region of the focal zone.
  • the control of cavitation in the sample also can be important during acoustic treatment processes.
  • the presence of small amounts of cavitation maybe desirable to enhance biochemical processes; however, when large numbers of cavitation bubbles exist they can scatter sound before it reaches the target, effectively shielding the sample.
  • Cavitation can be detected by a variety of methods, including acoustic and optical methods.
  • An example of acoustic detection is a passive cavitation detector (PCD) which includes an external transducer that detects acoustic emissions from cavitation bubbles.
  • the signal from the PCD can be filtered, for example using a peak detector followed by a low pass filter, and then input to a controlling computer as a measure of cavitation activity.
  • the acoustic signal could be adjusted in ways similar to those described in the temperature control example to maintain cavitation activity at a desired level.
  • Overpressure Increased ambient pressure is one technique for controlling cavitation. Overpressure tends to remove cavitation nuclei. Motes in the fluid are strongly affected by overpressure and so cavitation in free-fluid is often dramatically reduced, even by the addition of one atmosphere of overpressure. Nucleation sites on container walls tend to be more resistant to overpressure; however the cavitation tends to be restricted to these sites and any gas bubbles that float free into the free-fluid are quickly dissolved. Therefore cells in the bulk fluid are typically unaffected by cavitation sites restricted to the container walls. Overpressure may be applied to the treatment vessel, the array of treatment vessels, the treatment bath and tank, or to the entire apparatus to achieve a higher than atmospheric pressure in the region of the focal zone.
  • Degassing Reducing the gas content of the fluid tends to reduce cavitation, again by reducing cavitation nuclei and making it harder to initiate cavitation. Another method of controlling cavitation or the effects of cavitation is to control the gasses that are dissolved in the sample fluid. For instance, cavitation causes less mechanical damage in fluid saturated with helium gas than in fluid saturated with argon gas.
  • Treatment vessels are sized and shaped as appropriate for the material to be treated. They can be any of a variety of shapes.
  • treatment vessels 502, 504, 506 can have vertical walls, can have a conical shape, or can have a curved shape, respectively.
  • certain treatment vessel 502, 506, prior to treatment with sonic energy have an upper member 530 and a lower member 550 which together form an interior region that contains the material 540 to be treated.
  • the ultrasound transducer projects a focused ultrasound beam upwards. The ultrasound beam penetrates the lower member 550 of the treatment vessel 502, 506 to act upon the contents 540 of the treatment vessel 502, 506.
  • the upper member 530 serves to contain the contents 540 of the vessel 502, 506.
  • the lower member 550 of the treatment vessel 502, 506 is configured to transmit the maximum amount of ultrasound energy to the contents 540 of the vessel 502, 506, minimize the absorption of ultrasound energy within the walls of the vessel 502, 506 and maximize heat transfer between the contents 540 of the treatment vessel 502, 506 and, for example, an external water bath.
  • the treatment vessel is thermoformed from a thin film in a hemispherical shape.
  • the film should have an acoustic impedance similar to that of water and low acoustic absorption.
  • One preferred material is low density polyethylene.
  • Alternative materials include polypropylene, polystyrene, poly(ethylene teraphthalate) ("PET”), and other rigid and flexible polymers.
  • the film may be a laminate to facilitate thermal bonding, for example using heat sealing. Thicker, more rigid materials may also be employed. Available multi-well plates in industry standard formats such as 96 well and 24 well formats may be employed with or without modification. Industry standard thick- wall, multi-well plates with thin film bottoms may also be employed. These can work particularly advantageously where the size of the focal zone of the ultrasound beam is smaller than a well. In this case, little energy is absorbed by the sides of the treatment vessel and, as a result, relatively little energy is converted to heat.
  • the upper member of the treatment vessel contains the contents in the vessel during treatment and can act also as an environmental seal.
  • the upper member of the treatment vessel can be flat or domed to enclose the interior of the treatment vessel.
  • the upper member of the treatment vessel may be made of a rigid or flexible material. Preferably, the material will have low acoustic absorption and good heat transfer properties.
  • the upper member of the treatment vessel is a thin film that can be bonded to the lower member, and the lower or upper member can be easily rupturable for post-treatment transfer of the treated material.
  • the upper and lower members of the treatment vessel may be joined together by thermal bonding, adhesive bonding, or external clamping. Such joining of the upper and lower members can serve to seal the contents of the vessel from contaminants in the external environment and, in an array of vessels, prevent cross-contamination between vessels. If the bond is to be achieved by thermal bonding, the upper and lower members of the treatment vessels may be made of film laminates having heat bondable outer layers and heat resistant inner layers.
  • the treatment vessel may be configured as a single unit, as a multiplicity of vessels in an array, or as a single unit with various compartments.
  • the upper and lower members of the vessel or array of vessels can be used once or repeatedly. There also can be a separate frame or structure (not shown) that supports and/or stiffens the upper and lower members of the vessel(s).
  • This frame or structure may be integral with the vessels or may be a separate member.
  • An array of treatment vessels may be configured to match industry standard multi-well plates.
  • the treatment vessel is configured in an array that matches standard 96 well or 24 well multi- well plates.
  • the frame or supporting structure holding the array of treatment vessels can have the same configuration and dimensions as standard multi-well plates.
  • a treatment vessel 508 can include a funnel 592 to facilitate transfer of the contents 540 from the treatment vessel 508 to a separate vessel 598 after treatment.
  • the funnel 592 can have a conical shape and include an opening at the narrow end.
  • the funnel 592 can be rigid, relative to the upper 530 and lower members 550 of the treatment vessel 508.
  • the large end of the funnel 592 is proximate the upper member 550 of the treatment vessel 508 and aligned with the treatment vessel 508.
  • the volume of the funnel 592 can be marginally less than the volume of the treatment vessel 508.
  • One process of transferring the contents 540 of the treatment vessel 508 to another post-treatment vessel 598 includes the following steps.
  • the upper member 530 of the treatment vessel 508 may be pierced with a sharp instrument or ruptured when a vacuum is applied.
  • the member 530 may be manufactured from a thin fragile material or made weak by etching a feature into the surface.
  • the treatment vessel 508 is inverted over the post-treatment vessel 598 in a vacuum fixture.
  • a filter 594 may be placed between the treatment vessel 508 and the post-treatment vessel 598 to separate solids 596 from the liquid 542 that is removed from the treatment vessel 508.
  • the filter 594 may be incorporated into the outlet of the funnel 592.
  • This arrangement of treatment vessel 508 and funnel 592 may be configured as a single unit or as an array of units. This array may match an industry standard.
  • the treatment vessel 508 should form a vacuum seal with a vacuum fixture (not shown) such that a pressure differential can form between the sample in the treatment vessel and the supplied vacuum. Once the vacuum is applied to the fixture, the pressure differential across the upper member 530 will cause the upper member 530 of the treatment vessel 508 to rupture and cause the lower member 550 to collapse into the funnel 592.
  • the lower member 550 should have sufficient strength so that it does not rupture where it bridges the opening in the small end of the funnel 592.
  • the pressure differential will cause the solid contents 596 of the treatment vessel to be squeezed between the flexible lower member 550 of the treatment vessel 508 and the relatively rigid funnel 592. This causes fluid 542 to be expelled from the solid materials 596 and collected in the post-treatment vessel 598.
  • a treatment vessel can be an ampoule, vial, pouch, bag, or envelope.
  • These and other treatment vessels can be formed from such materials as polyethylene, polypropylene, poly(ethylene teraphthalate) (PET), polystyrene, acetal, silicone, polyvinyl chloride (PVC), phenolic, glasses and other inorganic materials, metals such as aluminum and magnesium, and laminates such as polyethylene/aluminum and polyethylene/polyester.
  • PET poly(ethylene teraphthalate)
  • PVC polyvinyl chloride
  • phenolic, glasses and other inorganic materials such as polyethylene/aluminum and polyethylene/polyester.
  • certain embodiments of a treatment vessel can be made by vacuum forming, injection molding, casting, and other thermal and non-thermal processes.
  • capillary tubes, etched channels, and conduits may be the sample holder during treatment as the sample flows through a structure. Additionally, free-falling drops, streams, non-moving free volumes, such as those in gravity less than one g, or a layer in a density gradient can be treated directly.
  • A. Biological Materials Many biological materials can be treated according to the invention.
  • such materials for treatment include, without limitation, growing plant tissue such as root tips, meristem, and callus, bone, yeast and other microorganisms with tough cell walls, bacterial cells and/or cultures on agar plates or in growth media, stem or blood cells, hybridomas and other cells from immortalized cell lines, and embryos.
  • other biological materials such as serum and protein preparations, can be treated with the processes of the invention, including sterilization.
  • Binding reactions involve binding together two or more molecules, for example, two nucleic acid molecules, by hybridization or other non-covalent binding. Binding reactions are found, for example, in an assay to detect binding, such as a specific staining reaction, in a reaction such as the polymerase chain reaction where one nucleotide molecule is a primer and the other is a substrate molecule to be replicated, or in a binding interaction involving an antibody and the molecule it binds, such as an immunoassay. Reactions also can involve binding of a substrate and a ligand.
  • a substrate such as an antibody or receptor can be immobilized on a support surface, for use in purification or separation techniques of epitopes, ligands, and other molecules.
  • Organic and inorganic materials can be treated with controlled acoustic pulses according to the methods of the invention.
  • the sonic pulses may be used to comminute a solid material, particularly under a feedback control regime, or in arrays of multiple samples.
  • individual organic and inorganic samples in an array can be treated in substantial isolation from the laboratory environment.
  • materials can be dissolved in solvent fluids, such as liquids and gasses, or extracted with solvents.
  • solvent fluids such as liquids and gasses
  • dissolution of polymers in solvents can be very slow without stirring, but stirring multiple samples with current methods is difficult and raises the possibility of cross- contamination between samples.
  • stirring of multiple samples without cross- contamination between samples can be accomplished with apparatus and methods of the invention.
  • Altering Cell Accessibility Sonicators can disrupt cells using frequencies around 20 kHz. It is generally thought there are two ways in which ultrasound can affect cells, namely by heating and by cavitation, which is the interaction of the sound wave with small gas bubbles in the sample. Heating occurs primarily due to absorption of the sound energy by the medium or by the container. For dilute aqueous systems, it is absorption by the container that is a main source of the heating. Heating is not desirable in some treatment applications, as described herein. The heating associated with the compression and cooling associated with the rarefaction of a sound wave is relatively small, even for intense sound.
  • controlled sonic pulses in a medium are used to treat a sample containing biological material.
  • the pulses can be specifically adapted to preferentially interact with supporting matrices in a biological material, such as plant cell walls or extracellular matrices such as bone or collagen, thereby lessening or removing a barrier function of such matrices and facilitating the insertion of extracellular components into a cell.
  • the cell is minimally altered and cell viability is preserved.
  • These pulses can be caused by shock waves or by sound waves.
  • the waves can be created external to the sample, or directly in the sample, via applied mechanical devices. In experiments where thermal effects are negligible, there typically is no lysis, unless cavitation is present.
  • sonic energy can have different effects than disrupting a matrix and can be used either with pre-treatment, with disrupting sonic energy, or by themselves.
  • the conditions to disrupt a matrix can be different from those to permeabilize a cell membrane.
  • cavitation may affect cells and there is no consensus as to which mechanisms, if any, dominate.
  • the principle mechanisms are thought to include shear, microjets, shock waves, sonochemistry, and other mechanisms, as discussed more fully below.
  • Microjets Bubbles undergoing a violent collapse, particularly near a boundary, such as a container wall, typically collapse asymmetrically and generate a liquid jet of fluid that passes through the bubble and into the boundary. The speed of this jet has been measured to be hundreds of meters a second and is of great destructive power. It may play a major role in the destruction of kidney stones by acoustic shock waves and may be a possible way of destroying blood clots.
  • Shock wave Collapse of a bubble spherically can generate an intense shock wave. This pressure can be thousands of atmospheres in the neighborhood of the bubble. The compressive stress of the shock wave may be strong enough to cause cellular material to fail.
  • Sonochemistry The pressure and temperatures in the bubble during an inertial collapse can be extraordinarily high. In extreme examples, the gas can be excited sufficiently to produce light, termed sonoluminescence. Although the volume is small and the time duration short, this phenomenon has been exploited to enhance chemical reaction rates. The production of free- radicals and other sonochemicals may also affect cells. Other: Other factors also may be involved. Vessel walls may contribute cavitation nuclei.
  • a plastic vessel with an aqueous fluid may result in a standing wave field due to internal reflections, as a result of impedance mismatches between the fluid and the vessel walls.
  • Examples of sonolucent materials are thin latex and dialysis tubing. Tube rotation studies performed on continuous wave dosage with unfocused ultrasonics indicate that rotation has a significant effect on hemolysis. When cell contents were mechanically stirred during insonation, the cell lysis increased. These effects may be due to viscosity gradients set-up within the unfocused ultrasound field that block energy transmission.
  • Cellular lysis also can be aided by the addition of ultrasound contrast agents, such as air- based contrast agents or perfluorocarbon-based contrast agents.
  • ultrasound contrast agents such as air-based contrast agents or perfluorocarbon-based contrast agents.
  • air-based contrast agent is a denatured albumin shell with air such as Albunex, available from
  • a perfluorocarbon-based contrast agent is a phospholipid coating with perfluoropropane gas such as MRX-130, available from ImaRx Pharmaceutical Corp., Arlington, AZ.
  • Air bubbles can block or reflect energy transmission. Interfaces between air and water result in efficient reflection of an incident ultrasound field.
  • the treatment dose is a complex waveform. Sections, or components, of the waveforms can have different functions. For example, the waveform can have three components involved with sample mixing, sample lysis/disruption, and sample cooling.
  • sonolytic yield activity decreases with increasing cell concentrations in in vitro systems that are treated with continuous ultrasound waves.
  • methods according to the present invention disrupt tissue structures with a complex waveform of high intensity focused ultrasound, to avoid this problem.
  • Mixing can be an important, because it allows bubbles that may have been driven by radiation forces to the edges of the vessel chamber to be brought into contact with the cell or tissue membranes. This mixing promotes inertial, transient acoustic cavitation near the cell walls, resulting in cellular lysis.
  • the acoustic dosage received by a sample can be likened to a radiation dosage received by a sample.
  • a computer-controlled positioning system can control the cumulative energy dosage that each sample receives.
  • a software program in the computer can actively control the cumulative energy dosage by treating the sample until the system reaches a particular set-point, pausing energy application or otherwise allowing the sample to reequilibriate, and reinitiating energy application to allow a sample to receive a higher cumulative dose while maintaining semi-isothermal conditions, such as a 1 to 2 degree Centigrade temperature rise during exposure, than would otherwise be possible by continuous sonic energy application.
  • This type of system enables high energy to be introduced into a sample while maintaining thermal control of the process.
  • controlled pulses in a medium can be used to treat a sample containing biological material to extract a fraction or fractions of the biological material.
  • the pulses are specifically adapted to preferentially interact with supporting matrices, such as plant cell walls or extracellular matrices such as bone or collagen, or materials having differences in rigidity or permeability in a biological material, thereby lessening or removing a barrier function of such matrices or materials.
  • These pulses can be caused by shock waves or by sound waves.
  • the waves can be created external to the sample, or directly in the sample, via applied mechanical means. Using sound energy, as opposed to laser or other light energy to disrupt a biological object, can be useful.
  • Sound is a direct fluctuation of pressure on the sample.
  • Pressure is a physical quantity and the measure of uniform stress defined as the force per unit area.
  • the stress acting on a material induces strain which changes dimensions of the material.
  • the two main types of stress are a direct tensile or compressive stress and shear stress.
  • the more brittle the material the greater the disruptive effect of an abrupt, local increase of otherwise uniform stress.
  • Such a local stress can be created by some geometric change at a surface or within the body of the sample. For example, biological tissue frozen at -70°C may be more prone to stress fracture than at 4°C.
  • a sharper change in geometric or material properties tends to cause a greater stress concentration, which in turn can yield a greater disruption. Sound waves may be focused.
  • the energy transferred from a light source such as a laser to a sample is electromagnetic radiation that induces non-ionizing molecular vibrations and breaks chemical bonds by ionizing.
  • Mechanical stress on objects larger than molecules generally cannot be readily caused by electromagnetic waves, except via destructive local heating.
  • the supporting matrix of a biological sample can be disrupted without disrupting one or more selected internal structures of the cells contained within the matrix.
  • Representative examples of such samples are: i) bone, in which a rigid matrix contains living cells of interest; ii) mammalian tissue samples, which contain living cells embedded in a matrix of elastic connective tissue and "glycocalyx" or intercellular matrix; and iii) plant tissues, such as leaves, which contain cells in a matrix of cellulose, often crosslinked with other materials, of moderate rigidity.
  • Virtually all living cells are gelatinous in texture, and can be deformed to some extent without rupture or internal damage.
  • Matrices in contrast, are designed to support and protect cells, as well as to achieve other biological functions.
  • the matrices of bone and leaves are designed to provide rigidity to the structure, while the support of most collagenous matrices has a strongly elastic character.
  • different protocols for example, amplitude, duration, number of pulses, and temperature of sample, may be used to disrupt different matrices by mechanical means without damaging the cellular material.
  • a bony matrix is both more rigid and denser than the cells it contains. Bone is vulnerable to shock waves, both because the calcified matrix will absorb the waves more efficiently than will the cells, and because the calcified matrix is weak under extensional strain, and thereby can fragment at stresses which will not damage the softer cells. Similar considerations apply to leaf matrix, although the contrast in density and modulus is less. In either case, a pulse, preferably a shock wave, is applied at an amplitude which is sufficient to fatigue the matrix components while remaining below the amplitude required to damage the cells. This intensity is determined readily for a particular type of sample by minimal routine experimentation.
  • the amplitude of each pulse applied to the sample is varied to obtain the maximum rate of degradation of the matrix consistent with retention of the viability of the cells within the matrix.
  • matrix degradation can be measured by variation in the compressive modulus of the sample, while cell integrity is measured by dye exclusion from cells extracted from the matrix, such as, for bone, demineralization and treatment with collagenase.
  • the pulses are selected to excite preferentially vibrational modes in the matrix in contrast to the cells.
  • a sequence of pulses may be required to differentially fatigue the matrix. The length of the pulses and the interval between them are adjusted so that the degree of heating of the sample does not cause loss of integrity of the cells, and particularly of the critical components which are to be isolated.
  • Treatment waveform Three areas to optimize for extraction are treatment waveform, mixing waveform, and positioning or dithering.
  • One method to determine the appropriate treatment and positioning parameters for a target sample for extraction purposes is described below.
  • a solid sample is placed in a volume of liquid in about a 1:1 ratio (weight/volume), in a treatment vessel.
  • a treatment vessel For example, 0.25 ml of methanol is added to 0.25 gm of leaf tissue in a 0.5 ml treatment vessel.
  • a single sample is placed within the focal zone of the sonic apparatus.
  • the mixing waveform is adjusted to provide "stirring" of the sample at the lowest amplitude, fewest cycles/burst, and lowest duty cycle.
  • the disruption treatment waveform is adjusted by immobilizing the target sample in the focal zone such that there is no mixing and no sample movement, such as dithering.
  • the sample is subjected to a minimum number of cycles per burst, for example, three.
  • the amplitude is initially used with a nominal 500 mV setting.
  • a portion of the sample is treated and inspected under a microscope for signs of membrane disruption. Such inspection can be done in conjunction with dyes that stain intracellular organelles.
  • the number of cycles/burst is then increased until a particular desired tissue disruption level is achieved in the immobilized portion of tissue.
  • the temperature of the sample is monitored during a million cycle total treatment with an infra-red sensor directed to the top of a thin polyethylene film covering the sample vessel.
  • the duty cycle is adjusted to keep the temperature within predefined ranges, such as 4°C within +/-2°C.
  • a control unit can be programmed with these data in order to control treatment of other samples of the same or similar biological type.
  • information can preprogrammed in the control unit, and an apparatus user, through a user input interface, can designate the biological material type to be treated such that the controller then runs through the predetermined treatment cycle.
  • Other information can be empirically determined for optimal treatment of a particular biological material in a manner similar to that described above. For example, parameters such as treatment waveforms, mixing waveforms, and sample positioning can be discerned. These parameters can vary depending upon the particular biological material, the particular liquid that surrounds the sample, and/or the particular treatment vessel used during treatment.
  • the cell in situations where a cell to be treated is not situated within a matrix, the cell can be directly treated according to the process below without having to pre-treat the matrix. While the treatment below is described mainly for transfection, methods and apparatus according to the invention are equally applicable to a transformation process or other processes to introduce an exogenous material into a permeabilized cell membrane.
  • cool temperatures less than 25°C, preferably less than 15°C, more preferably 4°C or below, tend to minimize the degradative effects of enzymes in the sample and thereby tend to preserve the integrity of biological components to be isolated.
  • cells especially mammalian cells, may maintain their viability better at higher temperatures, such as 30 to 37°C. These temperatures also allow enzymes to be added to aid in the selective destruction of the matrix.
  • the sample temperature may be below 0°C. Except under special conditions, this will freeze the sample, or maintain it in a frozen state. Freezing can be advantageous if it enhances the disruption of the matrix while allowing the cell to remain relatively intact. For example, ice crystals formed on freezing can be selectively larger outside of cells. Since such crystals may tend to absorb acoustical energy better than water, destruction of the matrix may be enhanced. While decreasing cell viability and integrity, such a procedure could enhance the ease of transfection with exogenous material after thawing of the sample.
  • the waveforms used to alter the permeability of a cell are refined depending on the particular application.
  • the shock wave is characterized by a rapid shock front with a positive peak pressure, for example about 100 MPa, and a negative peak pressure, for example about negative 10 MPa.
  • This waveform is of a few microsecond duration, on the order of about 5 microseconds. If the negative peak is greater than about 1 MPa, cavitation bubbles may form. Cavitation bubble formation is also dependent upon the surrounding medium. For example, glycerol is a cavitation inhibitive medium; whereas, liquid water is a cavitation promotive medium. The collapse of cavitation bubbles forms "microjets" and turbulence that impinge on the surrounding material.
  • Sound waves namely acoustic waves at intensities below the shock threshold, provide an alternative means of disrupting the matrix to allow access to the plasma membranes of the cells to allow transformation.
  • Such sound waves can be generated by any known process.
  • subzero temperatures for example about negative 5°C
  • most but not all of the water is in the solid phase.
  • micro- domains of liquid water still remain for several reasons, such as natural "antifreeze" molecules or regions of higher salt concentration. Therefore, as a sample temperature is varied during the treatment with sound or shock waves, microdomains of liquid water are able to form shock waves and induce cavitation bubble formation and collapse, with the resultant shear stresses that impinge on surrounding tissues.
  • the waves can be applied to the samples either directly, as piezoelectric pulses, or via an intervening medium.
  • This medium may be water, buffer, stabilizing medium for the target material to be isolated, or extraction medium for the target.
  • An intervening medium also can be a solid, formed of a material which is intrinsically solid, or of a frozen solution. Waves also can be applied through a container, such as a microtiter plate.
  • the techniques useful for disrupting matrix structure can be adapted, and the improved technique can be used, to facilitate the incorporation of exogenous material into cells.
  • the exogenous material may be DNA, RNA, other nucleic acid constructs, nucleic acid monomers, plasmids, vectors, viruses, saccharides, polysaccharides, amino acids, amino acid chains, enzymes, polymers, organic molecules, inorganic molecules, proteins, cofactors, and/or visualization reagents such as fluorescent probes.
  • shock waves or sonic waves are used to loosen the matrix, essentially as described above.
  • the intensity of application of acoustic energy is kept sufficiently short, or below a critical energy threshold, so that cell integrity is completely maintained, as verified by a method such as dye exclusion.
  • a solution or suspension containing the material to be inco ⁇ orated into the cells is added to the sample.
  • the exogenous material is incorporated into the cells in a conventional manner, as is known in the art for cells with exposed plasma membranes.
  • acoustic energy is used to transiently permeabilize a plasma membrane to facilitate introduction of exogenous materials into the cells.
  • the exogenous material may be present in the sample during the weakening of the matrix by acoustic energy.
  • the process of weakening the cell matrix by acoustic energy transiently destabilizes the plasma membranes, increasing the uptake of exogenous macromolecules and structures. If a further increase in the rate of incorporation is needed, then the intensity or time of application of acoustic energy is slightly increased until the cell membrane becomes transiently permeable. For example, a gentle pulse or wave is applied to the mixture, with a predetermined amplitude. This amplitude can be determined readily in separate experiments on samples of the same type to transiently make a plasma membrane of a cell type porous, in a similar empirical manner to the steps described above for determining an appropriate treatment to disrupt a matrix. During the transient porous state, exogenous materials diffuse into the cell and the materials are trapped there once the sonic or shock pulse is removed.
  • a major advantage of these methods for transfection, or other incorporation of exogenous material into living cells is that the methods are readily amenable to scale-up, to automation, and to marked reduction in sample size and reagent volume.
  • the wells of microplates can be used for sonic treatment, transfection, and post-transfection demonstration of successful incorporation of the added material.
  • extracellular non-incorporated reagent for example a fluorescent material
  • extracellular non-incorporated reagent for example a fluorescent material
  • extracellular non-incorporated reagent for example a fluorescent material
  • extracellular non-incorporated reagent for example a fluorescent material
  • a material that does not pass the cell membrane such as an enzyme, or certain hydrophilic or amphiphilic small-molecule reagents.
  • the presence or absence of the required material can be determined directly in the sample, for example by spectroscopy.
  • the methods are adaptable to large scale automation, in large part because they do not require the isolation of the cells from their matrix.
  • the permeabilized cells can be transformed or transfected, using techniques known to those skilled in the art, for example, electroporation, vacuum transfection, or using viral vectors, agrobacterium, liposomes or other delivery vehicles, plasmids, or naked nucleic acids.
  • the buffer conditions may be altered during the process.
  • the initial permeabilization may occur with chemicals to selectively alter the external cell wall, while during the nuclear wall permeabilization step, other chemicals or biochemicals may be added to prompt selective uptake.
  • sample mixing is conventionally performed by vortexing or stirring, or other methods such as inversion of a sample containing an air space, and shaking.
  • Vortexing is essentially achieved by mechanical motion of the entire vessel while stirring involves mechanical contact of a driven device with a fluid.
  • Stirring is accomplished with a variety of devices, for example with propellers, impellers, paddles, and magnetic stir bars.
  • propellers, impellers, paddles, and magnetic stir bars One problem with these methods is that it is difficult to increase their scale in order to handle dozens or hundreds of sample vessels at once.
  • Another problem with these methods is the difficulty of mixing multiple samples while keeping the each sample substantially free from contamination.
  • methods according to the invention can use sonic energy to mix a sample while avoiding problems with contamination. More particularly, factors, such as focusing the sonic energy, as well as otherwise controlling an acoustic waveform of the sonic energy to be directed at one or more nucleation sites, and selectively locating nucleation sites can be used to selectively mix a sample, for example, through acoustic streaming and/or microstreaming.
  • a fluid sample can be mixed controllably using the system described herein. No direct contact between the material to be mixed and the sonic energy source is required. However, in some embodiments, contact is preferable.
  • the material to be mixed is in a treatment vessel, such as a microplate, the treatment vessel itself is not necessarily touched by the source and is typically coupled to the source by a fluid bath.
  • the acoustic source is a microsource located within a microdevice chamber.
  • a treatment process for sample mixing in a treatment vessel can be summarized as follows. First, a sample is treated with sonic energy at a relatively high first treatment power in order to heat the sample by absorption of acoustic energy.
  • the sample is mixed at a second sonic energy power, which may be the same or lower than the first treatment power, to cool the sample back to its original temperature by forcing convection through material in the treatment vessel, which can be in contact with a fixed-temperature bath or reservoir.
  • a second sonic energy power which may be the same or lower than the first treatment power
  • a source of focused ultrasonic waves is used.
  • the source is mounted in a water bath or equivalent, which can provide temperature control.
  • the microplate, with samples in the wells, is positioned so that the focus of the beam is within the well.
  • the plate is positioned so that the bottoms of the wells are in contact with or immersed in the water or other fluid in the bath.
  • a burst of ultrasonic energy is applied to the well. This burst will cause stirring in the well, by formation of a convection cell.
  • the stirring is easily visualized by adding particulate material to the wells, or by adding a dye in a denser or lighter solution.
  • a substantially uniform field is projected to the plate by a source, which preferentially excites the bottoms of the wells. This excitation in turns drives convective flow in each of the wells.
  • nucleation features are located in the plate proximate to each of the wells, or even inside the wells, to enable mixing to occur at lower energy levels.
  • Dithering or other types of motion, can even out variations in source intensity due to variations in the emitted sonic energy or the location of the sample with respect to the source. Dithering can also prevent particulates from accumulating at the wall of the well. Fluid control features, such as mixing, are discussed below in further detail with respect to Figures 8-17.
  • temperature, mixing, or both can be controlled with ultrasonic energy to enhance a chemical reaction.
  • association rate between a ligand present in a sample to be treated and an exogenously supplied binding partner can be accelerated.
  • an assay is performed where temperature is maintained and mixing is increased to improve association of two or more molecules compared to ambient conditions. It is possible to combine the various aspects of the process described herein by first subjecting a mixture to heat and mixing in order to separate a ligand or analyte in the mixture from endogenous binding partners in the mixture.
  • the temperature, mixing, or both are changed from the initial condition to enhance ligand complex formation with an exogenously supplied binding partner relative to ligand/endogenous binding partner complex formation at ambient temperature and mixing.
  • the second temperature and/or mixing conditions are intermediate between ambient conditions and the conditions used in the first separating step above. At the second temperature and mixing condition, the separated ligand is reacted with the exogenously supplied binding partner.
  • One of the bottlenecks of the PCR technique is cooling time.
  • the heating cycle is rapid; however, cooling is limited by convection.
  • certain embodiments of the invention can be used to overcome this bottleneck.
  • a treatment process can be used to both heat and cool the sample rapidly with little overshoot from a baseline temperature at which the primer and target to be amplified anneal.
  • the process can be summarized as follows.
  • a sample is treated with relatively high power sonic energy such that the sample absorbs sonic energy and is heated.
  • the sample is mixed at low power to cool the sample by forcing convection, which may be accomplished in conjunction with a cool water bath.
  • the system is a "dry top" system, that is, a system in which a microplate, typically with its top temporarily sealed with plastic film, floats on or is partially immersed in a controlled- temperature bath.
  • the PCR reaction may be monitored in real-time for temperature, using, for example, an infra-red detection probe, and for reaction products by examining the incorporation of fluorescent dye tagged nucleic acid probes into the PCR product.
  • This "dry top" system permits real-time analysis and control of the process.
  • Information from the temperature sensor can be used in a feedback loop to control the duty cycle of the acoustic input , such as the number of bursts/second, or otherwise control the amount of heating.
  • fluorescence from an intercalated probe can provide a computer with information on which wells have reached a certain point in the reaction, such as when a particular level of fluorescence is sensed, allowing, for example, the computer to control application of sonic energy or sample location such that certain wells are skipped in the processing cycle until other wells have attained the same point in the reaction or that certain wells are not processed further.
  • F. Purification, Separation, and Reaction Control Focused sonic fields can be used to enhance separations.
  • sonic foci can be used to diminish or eliminate wall effects in fluid flow, which is an important element of many separation processes, such as chromatography including gas cl romatography, size exclusion chromatography, ion exchange chromatography, and other known forms, including filed-flow fractionation.
  • chromatography including gas cl romatography, size exclusion chromatography, ion exchange chromatography, and other known forms, including filed-flow fractionation.
  • Sonic fields also can be used to minimize concentration polarization in membrane processes, including particle classification, filtration of fine particles and colloids, ultrafiltration, reverse osmosis, and similar processes. Concentration polarization is the result of the tendency of filtered material to be present at high concentration in a layer on the filter.
  • This layer has a low fluid concentration and, thus, diminishes the rate of filtration as the filtered solution becomes more concentrated, or as the layer thickens.
  • This layer can be stirred remotely by focused sonic energy of low to moderate intensity. Flow rate, thus, can be enhanced without significant cost in energy or membrane life.
  • Such sonic energy fields can be used to enhance reaction rates in a viscous medium, by providing remote stirring on a micro scale with minimal heating and/or sample damage.
  • some assays rely on the absorption of analytes by reagents, such as antibodies, which are bound to macroscopic particles.
  • reagents such as antibodies
  • a viscous fluid to be analyzed such as sputum or homogenized stool
  • the ability to stir such a sample remotely, aseptically, and essentially isothermally can significantly decrease the time required to obtain equilibrium of the analyte with the reagents on the particle.
  • any bimolecular (second-order) reaction where the reactants are not mixed at a molecular scale, each homogenously dissolved in the same phase, potentially can be accelerated by sonic stirring.
  • convection or stirring can potentially minimize local concentration gradients and thereby increase the rate of reaction.
  • This effect can be important when both reactants are macromolecules, such as an antibody and a large target for the antibody, such as a cell, since their diffusion rates are relatively slow and desorption rates may not be significant.
  • remote sonic mixing provides a substantially instantaneous start time to a reaction when the sample and analytical reagents are of different densities, because in small vessels, such as the wells of a 96 or 384 well plate, little mixing will occur when a normal- density sample (about 1 g/cc) is layered over a higher-density reagent mixture.
  • Remote sonic mixing can start the reaction at a defined time and control its rate, when required.
  • the stepping and dithering functions allow multiple readings of the progress of the reaction to be made.
  • the mode of detecting reaction conditions can be varied between samples if necessary. In fact, observations by multiple monitoring techniques, such as the use of differing optical techniques, can be used on the same sample at each pass through one or more detection regions.
  • Control of sonic energy emission, sonic energy characteristics, and/or location of a target relative to sonic energy also can be used to pump and control the flow rate of liquids, especially in capillaries; enhance chemical reactions, such as enhancing second-order reaction rates; increase effective Reynolds number in fluid flow; and control the dispensing of semi-solid substances.
  • Sonic excitation provides a convenient, simple, and sterile manner to accelerate flow in capillaries. During excitation, the fluid is locally turbulent, and so flows more readily.
  • selective or timed local sonic excitation optionally controlled with a feedback loop, the rate of flow through complex microfluidic paths can be remotely manipulated in a controlled manner.
  • methods of the invention can not only be used to increase flow, but can also be used to inhibit flow. Increase of Effective Reynolds Number in Fluid Flow
  • Excitation of the near- wall fluid in a continuous, scanned, or burst mode can lead to rapid homogenization of the fluid composition just downstream of the excited zone. This will sharpen the front between any two fluids passing through a pipe in succession.
  • cavitation features can be located on or in the wall of a pipe to facilitate homogenization of the fluid flow, with the use of unfocussed acoustic energy. This effect is useful in several areas, including chromatography; fluid flow in analytical devices, such as clinical chemistry analyzers; and conversion of the fluid in a pipeline from one grade or type to another. Since most of the effect occurs in a narrow zone, only a narrow zone of the conduit typically needs to be sonically excited.
  • the focal zone of the sonic energy can be the region closest to a valve or other device which initiates the switch of composition.
  • feedback control can be based on local temperature rise in the fluid at a point near to or downstream of the excitation region.
  • Enhancement of Second-Order Reaction Rates Microsonication can be used to speed up, or to homogenize, the rate of chemical reactions in a viscous medium. The flow of individual molecules, and of heat, is generally slower in a more viscous medium. For example, it is more difficult to mix molasses with water than to mix vinegar with water.
  • a polymerase chain reaction can be accelerated by brief pulses of sonic energy, or by longer pulses which also provide the desired temperature increases, to prevent the retardation of the reaction due to local depletion of the nucleotide triphosphate monomers.
  • sonic energy or by longer pulses which also provide the desired temperature increases, to prevent the retardation of the reaction due to local depletion of the nucleotide triphosphate monomers.
  • similar results can be achieved with unfocussed sonic energy by selectively locating nucleation features to enable cavitation at lower energies.
  • Highly viscous liquids including materials which effectively act as solids or near-solids, can flow at an increased rate when sonically excited by a remote or local sonic source.
  • This excitation may be under feedback control.
  • This effect can be caused by local reduction of impedance to flow by walls of a conduit, as described above, and by local heating from sonic energy input.
  • the effective viscosity of an ink jet ink and thus the rate of its delivery, can be controlled by focused, localized sonic energy delivery.
  • Analogous uses are possible wherever the viscosity of a fluid, including a semi-solid or a solid capable of melting, is significant.
  • flow of particulate materials in a fluid where the particles are insoluble in the fluid can be selectively stimulated to occur, or be accelerated, with focussed, controlled sonic waveforms.
  • the acoustic source 230 and controller 410 may be fabricated integrally with a microdevice containing a liquid to be mixed or caused to flow.
  • the controller 410 may be fabricated as a separate remotely located component and communicatively coupled (for example, via an electrical or optical interface) to the source 230.
  • the acoustic source 230 may also be fabricated separately and located remotely from the microdevice. In such an embodiment, the acoustic source 230 couples to the microdevice for example, by way of a solid, liquid, gel, vapor or gas couplant.
  • the source 230 is fabricated to be located inside a microchamber of a microdevice, and is in direct contact with the fluid to be controlled.
  • the acoustic field energy 240 is sufficiently intense to at least form a bubble in a target zone 800 (which may correlate with the focal zone of the source if the source is focused).
  • the acoustic field 240 is sufficiently intense to alternate between bubble formation and bubble decay or collapse in the target zone 800. At still higher energies the acoustic field 240 causes bubble formation, streaming, and collapse at a location different from the nucleation site; this is preferred for some types of microfluidic applications, such as mixing in a fluid device.
  • the methodology of the invention includes two important aspects.
  • the invention directs the acoustic field 240 at through, for example, blocking, focussing, and/or reflection, at nucleation features to control fluid movement.
  • the invention provides nucleation features at selected locations and then interacts either focussed or unfocussed acoustic energy with the selectively located nucleation features to control fluid flow.
  • FIG 8 is a conceptual diagram 800 depicting an illustrative life cycle of a bubble formed on a surface 802 having a crevice or surface defect 804, which acts as a nucleation feature, according to an illustrative embodiment of the invention.
  • acoustic energy is directed toward the feature 804, cavitation occurs in a controlled, beneficial manner.
  • the acoustic energy 240 required for cavitation is lower with cavitation promoters, such as the nucleation feature 804, than without promoters.
  • a gas or vacuum pocket 808 forms and creates a liquid-gas (vapor) interface in the feature 804.
  • the pocket 808 grows to form a bubble 810 and locally displaces the fluid 806.
  • cavitation occurs in response to repeated cycles of negative and positive pressures from the acoustic field 240 and to increasing the energy of the field 240 above a threshold energy level.
  • the bubble 810 can be made to alternatingly increase (812) and decrease (814) in diameter.
  • the alternating rarefaction (812) and compression (814) process causes localized flow in the fluid 806 proximate to the feature 804, and thus creates a localized micromixing action.
  • the bubble 810 can collapse either slowly or abruptly. As shown at 816, in response to discontinuing the acoustic field 240, the bubble 810 dissipates back to the pocket 808, and thus ceases the micromixing action.
  • nucleation sites can be selective located anywhere that aids fluid control. It should also be noted that exposure to the acoustic field 240 may also cause heating of the device 802 and the fluid 806, and that, as described above, the effects of the field 240 can be changed by varying characteristics of the acoustic field 240. Also, the acoustic field 240 may or may not be particularly directed at the feature 807. Also, the feature 807 may be selectively located or may naturally occur as a result of the fabrication of the surface 202.
  • the acoustic field 240 may be a traveling wave field or a standing- wave field.
  • the frequency and other parameters of the acoustic field 240 may be varied to achieve and control the desired effects and minimize undesired effects.
  • the field 240 may be moved in a regular pattern relative to the microdevice containing the fluid to be mixed to achieve rapid results over the entire volume of the microdevice, or may be moved in a random or pseudo-random pattern to treat the microdevice in a stochastic manner.
  • the frequency of the acoustic field 240 may be varied over time.
  • the frequency may be swept upward during a tone burst to move the interference pattern closer to the axis and thus sweep material to the center.
  • a series of tone bursts at increasing frequencies may be applied to achieve the same effect.
  • a high frequency such as 1.1 MHz, may be applied to generate bubbles in the device and a lower frequency may then be applied to cause them to collapse.
  • a cavitation promoting feature is excited by 1.1 MHz acoustic energy produced by a 100 mV excitation of the transducer, then a pulse of 10 cycles will generate a bubble, producing waves in the solution tending to mix it locally. If the energy 240 is then turned off for 10 cycles, the bubble will collapse. Alternatively, the bubble may oscillate at an energy less than that required to initiate a bubble, such as 25 mV. (Note: these voltages are for a particular apparatus and are only being used illustratively.) Which mode of bubble removal is best will depend on the particular apparatus and purpose, and can be determined experimentally if required.
  • a microdevice, containing fluid to be mixed may or may not be near or at the focus of a focused acoustic field 240. If the microdevice is in or near the focal plane of a focused acoustic field 240, the intensity gradient in the plane of the microdevice will be at a maximum. If the microdevice is moved into the near field or the far field of the acoustic field 240, the intensity gradient in the plane of the microdevice will be lowered. The microdevice may be moved along the axis of the field 240 during or between treatments to effect mixing within the microdevice.
  • Illustrative experiments have employed both focused and unfocussed acoustic fields 240 at a certain frequency (about 1.1 MHz) oriented perpendicular to the plane of the microdevice. However, similar effects may be obtained with an unfocused field 240 whose direction of propagation is tilted relative to the plane of the microdevice or at a different or time- varying frequency. In addition, two or more acoustic fields 240 may be caused to interact or interfere in the microdevice to cause mixing.
  • the hybridization chamber such as that depicted at 1004 in Figure 10, is typically a planar device.
  • the apparatus of the invention may be arranged such that the acoustic field 240 can irradiate the device from either the base (bottom) 1016 side or the cover (top) 1014 side.
  • the acoustic source 230 may be integrally fabricated in an internal wall of the chamber 1004.
  • the features, such as 1006a and 1006b, that promote mixing may be located on either inside surface of the microdevice 1002 such that they are on either the near side or the far side relative to the acoustic field 240.
  • the axis of the acoustic field 240 may be perpendicular to the microdevice, parallel to the plane of the microdevice, or at an angle relative to the plane of the microdevice. Also, the acoustic field 240 may or may not be particularly directed at the nucleation features 1006a and 1006b.
  • Moving the microdevice 1002 relative to the acoustic field 240 during or between treatments can offer several advantages. Dithering (small variations in position around a center point) in the X-Y plane during treatment changes the intensity gradient in the plane of the microdevice 1002 and causes flow patterns to change direction and intensity. This causes more uniform mixing over larger areas. This may also cause better mixing in the comers of a square or rectangular hybridization chamber. Motion in the z (axial) direction causes changes in the interference pattern in a standing wave field, and may be used to break up aggregations of particles that may have formed.
  • the cavitation promoting features may be a single feature, such as a pit, or a multitude of features such as a field of pits or a hatch pattern of lines or grooves.
  • the device may be moved relative to the acoustic field 240 such that the flow pattern generated by the feature will vary with time.
  • the cavitation promoting feature may be dithered around the focal zone of a focused acoustic field 240 such that the flow pattern rotates around the feature.
  • the flow is directed in a single direction at any one point in time, but the flow direction is varied over time to water a large area uniformly.
  • turning on the acoustic field 240 causes mixing.
  • Turning it off causes mixing to stop.
  • the on and off intervals may be controlled to maximize mixing while allowing enough quiescent time or residence time or contact time for binding reactions or other chemical reactions to take place before the reactants are separated by another mixing event.
  • the temperature of the microdevice may be cycled up and down in coordination with the mixing intervals to influence the occurrence of reactions or the rate of reactions within the microdevice.
  • the cavitation threshold is the acoustic intensity at which cavitation begins at a particular region in a fluid.
  • the cavitation threshold is influenced by several factors including isotropic pressure, dissolved gas content and fluid composition as well as the presence or absence of nucleation features.
  • the acoustic field 240 may be operated above the cavitation threshold to cause beneficial cavitation effects in a microdevice or may be operated below the cavitation threshold to obtain other effects not related to cavitation, such as heating.
  • cavitation can be detected by means of a passive cavitation detection transducer and the appropriate electronics 700 or any of several other well known mechanisms.
  • This detection mechanism may generate an error signal for use in a feedback control mechanism to modulate the acoustic field 240.
  • the term "passive” implies that the detected signal is generated by cavitation.
  • An "active" cavitation detection system interrogates the region of interest with an external energy source (e.g., a laser light source) that is modulated by cavitation bubbles in the device.
  • a passive cavitation receiver transducer is positioned confocally with a source transducer of the acoustic field, such as the source transducers of Figure 6, or the source 230 of Figure 1.
  • the receiver transducer should have a frequency pass band higher than, and not substantially overlapping, the pass band of the source transducer. Cavitation signals of interest are generally higher than the source 230 frequency. Other embodiments include having overlapping pass bands combined with suitable filters or signal processing to suppress the source frequency from the receiver transducer signal. Another embodiment may involve using the source transducer itself as a receiver for cavitation detection. There are several methods of passive and active cavitation detection that are described in the literature. Any or all of these may be suitable for detecting cavitation in conjunction with the present invention.
  • cavitation promoting nucleation features and texture details are on the exterior of a sample chamber to affect the acoustic field within the chamber to promote bubble formation and streaming in the areas to be mixed in the interior. According to the illustrative embodiments, it is recognized that particles in a solution can lower nucleation thresholds similarly to "features" or “textures” on the walls of a chamber or passage.
  • FIG. 9 is a conceptual diagram 900 depicting the stages of nucleation in a microcavity according to an illustrative embodiment of the invention.
  • the substrate 902 includes a microcavity 904.
  • a naturally occurring or intentionally created crevice 906 is located within the microcavity 904.
  • the crevice 906 nucleates a small bubble 908.
  • the bubble 908 grows in diameter with each pressure cycle from the acoustic source 230 through rectified diffusion until it substantially fills the microcavity 904.
  • the gas/liquid interface 914 of the fully formed bubble 908 displaces the liquid fluid immediately adjacent to the interface 914, imparting localized fluid movement. This process may be repeated as necessary to create localized fluid movement.
  • frequency of the acoustic field 240 and the diameter of the resonant bubble 914 in a free aqueous fluid namely, frequency in Hertz multiplied by resonant the bubble radius is approximately equal to three meters/second.
  • frequency in Hertz multiplied by resonant the bubble radius is approximately equal to three meters/second.
  • a transducer having a frequency of about 1.1 MHz is focused, a resonant bubble of about radius of 2.7 microns forms.
  • a transducer having a frequency of about 11 MHz is focussed, a bubble having a radius of about 0.27 micron forms.
  • the relationship becomes more complicated when the bubble is in or influenced by a microcavity or concave feature on a surface.
  • this dimension is appropriate for microfluidic and micro-electro-mechanical-system (MEMS) type devices. It is an property of the invention that it is possible to utilize a 1.1 MHz focused transducer to control cavitation in a miniaturized device to regions having micron scale dimensions as the focal zone of this transducer is relatively large at about 2 x 6 mm.
  • MEMS micro-electro-mechanical-system
  • the mixing apparatus of the invention can be employed to micromix fluid surrounding an active detection or reaction site, such as a DNA spot in an array of DNA spots.
  • Figure 10 is a conceptual diagram 1000 depicting operation of an acoustic microstreaming-based mixing apparatus according to an illustrative embodiment of the invention.
  • Figure 10 shows a cross-section of a microfluidic device 1002 with an active detector site 1004, such as a spot containing DNA probes or an electrode.
  • the device 1002 also includes nucleation promoting features 1006a and 1006b.
  • the site 1004 may be placed on an independent zone 1008 that is acoustically masked from the active acoustic field 240.
  • the oscillation of the gas body or bubble 1010 in a fluid 1012 contained within a microchamber formed by the two structures 1014 and 1016 provides a local micromixing action around the feature 1006a indicated by the arrows 1018a and 1018b; and the oscillation of the bubble 1011 provides a local micromixing action around the feature 1006b indicated by the arrows 1020a and 1020b.
  • the invention can be employed to micro mix portions of the fluid 1012, without disturbing the active site 1004.
  • the acoustic source 230 and/or the controller 410 may be integrated with or remotely coupled to the device 1002.
  • the source 230 may be located either inside the chamber formed by the elements 1014 and 1016, or integrally formed to an external wall of one of the elements 1014 and 1016.
  • the acoustic source 230 can be located remotely as shown in Figure 1.
  • Figure 11 is a conceptual block diagram 1100 illustrating use of the mixing apparatus to locally mix fluid in a microdevice containing an array of active sites. More particularly, Figure 11 depicts a fabricated device 1102 including a plurality of active detector sites 1104, with each active site 1104 surrounded by a plurality of selectively placed nucleation features 1106. Although not shown, skilled artisans will appreciate that in practice, the microarray 1102 employs a cover, such as the element 1014 in Figure 10, to form a microchamber containing the array of active sites 1104 and nucleation features 1106.
  • nucleation features 1106 in response to exciting the nucleation features 1006 with the acoustic field 240, micromixing of the liquid occurs proximate to each active site 1104, without dislodging the active components contained in each site 1104.
  • Figure 11 depicts a specific arrangement of nucleation features 1106 around each active site 1104, skilled artisans will appreciate that the nucleation features 1106 may be located anywhere within the microchamber of device 1102 relative to the detector sites 1104, and that such location can be selected to effect fluid flow within the chamber. For example, if high fluid velocities or pulsating bubbles cause damage to the active sites 1104 in a particular device 1102, the nucleation features 1106 can be located a certain minimum distance from the detector sites 1104.
  • the active sites 1104 can be located away from the nucleation features 1106.
  • the relative positioning of the nucleation features 1106 and the active sites 1104 can be optimized to enhance flow of the chamber fluid past the active sites 1104 without scrubbing or otherwise damaging the active sites 1104.
  • nucleation features may be located in the active sites 1104 to effectuate mixing.
  • the acoustic source 230 may be located as depicted in Figures 1 and 7 relative to the microarray 1102. Alternatively, the acoustic source 230 may be integrally formed to the top (cover not shown) or bottom 1108 external surface of the array 1102, or contained within the array microchamber.
  • the invention may be utilized to accelerate synthesis and binding reactions at the active sites 1104.
  • the result is a controlled, micromixing apparatus capable of scaling the magnitude of mixing to the application required.
  • the sequential activation of bubbles such as those occurring at the nucleation features 1106, can be employed to produce a net directional flow in the surrounding fluid.
  • the invention can provide a compact testing device.
  • One particular application is in the formation of a DNA testing cassette.
  • the mixing apparatus is incorporated into a cassette holding a hybridization slide having a cover with fluid ports at either end. Connections are provided to fluidic reservoirs to wash with different solutions.
  • the mixing apparatus can be oriented vertically to enable gravity-based fluid flow to be accelerated with the sonic energy mixing.
  • the sonic energy field established can be used to provide energy to disrupt surface tensions to allow fluid flow across the array or other immobilized surfaces.
  • the mixing apparatus can be oriented horizontally with hydrostatic pressure differentials across the reaction chamber to drive the fluid transfer.
  • the surface tension of a low profile system (such as 100 micrometer gap height) may be altered with the sonic energy field to allow faster and more uniform slide processing.
  • nucleation features such as the feature 804 and the microcavity 904.
  • Such features reliably induce (nucleate) bubble formation and enable cavitation acoustic energies lower than that required to cause cavitation on relatively smooth surfaces or in solution.
  • nucleation features may be placed to control where cavitation occurs.
  • These nucleation features can be in the form of discrete point-like features, including but not limited to pits, crevices, craters, frustums, pins, posts spikes, spicules, bumps or linear features, including but not limited to scratches, grooves, ridges, or the like.
  • the nucleation features can be produced by diverse manufacturing methods including but not limited to scratching, etching, grinding, engraving, milling, drilling, sand blasting, ion-beam processing, molding, pressing, hot stamping, microlithography, micromachining, microfabrication or the like.
  • material properties such as acoustic impedance, density, modulus of elasticity, hydrophobicity, wetability, surface energy, distribution of impurities or contaminants on or in a surface, and the like can also preferentially nucleate cavitation.
  • These material variations may be formed by manufacturing processes including but not limited to ion implantation, plating, chemical modification, or the like.
  • Nucleation features can also be created by placement or formation of electrodes.
  • Geometric or material features may also be located on the outside of a device to promote cavitation on the inside of the microdevice by interacting with the acoustic field to cause intensity variations in the acoustic field coupled into the microdevice.
  • the multitude of features may be called a "texture".
  • the textures may be either ordered as in an array of features, as discussed above with respect to Figure 11, or include randomly distributed features.
  • the extent of textured areas may be controlled so as to promote cavitation in specific regions of a microdevice, such as discussed above with respect to the region surrounding each active site 1104 of Figure 11.
  • the creation of features and textures enables the generation, of zones of mixing and pumping which can be selectively activated by acoustic energy.
  • Bubbles may also be generated by other means, such as chemical reaction or by electrochemical processes.
  • bubble generation sites in the microdevice may have or contain an immobilized chemical species that will react with a species in the fluid either when brought into contact or in response to a change in condition such as a change in pH.
  • Another means of generating gas bubbles is by electrolysis at an electrode. Applying an appropriate electrical signal to an electrode in contact with an appropriate fluid in a microdevice will cause gas bubbles to form.
  • Electrochemical means of gas generation in the fluid of the microdevice can be controlled by modulating the electrical signal applied to the electrode.
  • Gas bubbles may be generated in regions in a device by arrays of chemically or electrochemically active features or by making an entire region chemically or electrochemically active.
  • the bubbles that are generated chemically or electrochemically may caused to grow by further gas production by chemical or electrochemical reaction or in response to an acoustic field.
  • the bubbles may then release and stream in response to an applied acoustic field.
  • the streaming bubbles cause fluid flow through viscous and momentum effects.
  • the size of the features or extent of a textured area may be smaller, even much smaller, than the focal zone of the acoustic field 240, if it is focused, or the extent of an unfocused field. This enables control of cavitation to a much smaller scale than a wavelength of the acoustic field 240.
  • the nucleation features are located to create rotational flow features that resemble the eddies that occur in turbulent flow.
  • the acoustic source 230 is direct at naturally occurring nucleation features to create rotational flow. Such an approach adds vorticity to what would otherwise be totally irrotational flow.
  • eddies are created near the walls or margins of conduits or cavities, which are the regions that are the most difficult to mix with alternative technologies. These eddies greatly enhance fluid exchange and mass transfer within the conduits or cavities of a small fluid microdevice.
  • the distribution of eddy sizes and loci within a microdevice can be tailored to resemble those of a turbulent flow field. The distribution of sizes and loci can be optimized for particular microdevices and applications such as flushing a microchamber or mixing reactants during a heterogeneous hybridization reaction.
  • Figures 12A and 12B depict the use of the apparatus to provide flow control in a microconduit. More particularly, in Figure 11A, the elements 1202 and 1204 are located to form an exemplary microconduit 1206. According to an illustrative embodiment of the invention, the element 1204 includes a nucleation feature 1208.
  • the nucleation feature 1208 may be naturally occurring, such as being the result of fabrication, or particularly created.
  • a gas pocket 1210 forms in the feature 1208.
  • the pocket 1210 forms into a bubble 1212.
  • the bubble 1212 effectively stops fluid flow, indicated by the arrow 1214. Upon cessation of the applied acoustic field 230, the bubble 1212 dissipates enabling fluid once again to flow through the conduit 1206.
  • the bubble 1212 functions essentially as a microflow control valve for conduit 1214. As discussed above, the acoustic field may be unfocused or particularly directed at the nucleation feature 1212.
  • acoustic mixing can effect mass transfer that would only occur otherwise as a result of diffusion.
  • the invention is especially useful in the case of reactions involving large biomolecules, where diffusion rates are extremely low. These reactions are rate limited by the diffusion of the reactants. Heterogeneous reactions involving a reactant that is bound to the surface of the reaction chamber, can be greatly accelerated using the methodology of the invention.
  • Figure 13 is a conceptual diagram 1300 depicting the use of the acoustic mixing apparatus to cause fluid flow in a microdevice according to an illustrative embodiment of the invention.
  • the elements 1302 and 1304 are located to create a microconduit 1306 though which fluid can flow (indicated by the arrows 1310).
  • the element 1304 includes a nucleation feature 1308 for promoting nucleation.
  • the nucleation features 1308 can be naturally occurring or particularly created and placed.
  • feature 1308 will generate and release cavitation bubbles. The released bubbles will stream in response to acoustic field intensity gradients.
  • Figures 14A-14D are conceptual diagrams depicting an alternative embodiment of the invention for providing fluid pumping.
  • Figures 14A-14D depict progressive states of a microdevice 1402.
  • the microdevice 1402 includes a series of acoustic transducers 1404a-1404c, a chamber 1406 containing fluid having the moieties 1408, and textures 1410 formed in a surface 1412.
  • the nucleation features 1410 can be naturally occurring during fabrication or particularly formed and positioned.
  • the acoustic transducers 1404a- 1404c can be integrally fabricated with the microdevice 1402 or can be remotely located.
  • the acoustic transducers 1404a- 1404c can be separate, individual transducers, or alternatively, a single remotely located source can be directed at any one or all of the regions 1416a-1416c of the microdevice 1402.
  • the controller 410 is not shown, but may be included in the device 1402 or may be communicatively coupled to the acoustic transducers 1404a-1404c.
  • the moieties 1408 can be moved from zone 1416a to 1416b.
  • the bubble 1414 can be formed to flow the moieties 1408 into zone 1416c.
  • the transducers 1404a, 1404b and 1404c in sequence, the bubble 1414 can be formed to flow the moieties 1408 to the far edge of zone 1416c.
  • the moieties 1408 may be processed or analyzed differently in each of the zones 1416a- 1416c.
  • a biological tissue sample such as the sample 1408, may be inserted into a device, such as the device 1402 in a particular zone, such as the zone 1416a.
  • the tissue 1408 can be introduced to a disruptive acoustic energy field from the transducer 1404a and the disrupted tissue 1408 is then ready for reagent addition.
  • the reagent addition may occur in zone 1416b, which has acoustic mixing conditions (e.g., to accelerate enzyme reactions).
  • the reaction products may then be transferred to zone 1416c and the binding (e.g., hybridization) events may be improved with acoustic energy.
  • One integrated device 1402 may have multiple zones for different processes, so that all of the above processing can occur on a single device.
  • the microdevice 1402 may, for example, be inserted into an external acoustic field, or processing can be accomplished by on-board acoustic field generation. This is especially appropriate for very small sample masses, for example, in the microgram to picogram range.
  • Figure 15 is a conceptual diagram 1500 depicting the use of the invention for mixing a solution on a microscope slide. More specifically, the diagram 1500 shows a microscope slide 1502 having a nucleation site 1504. The liquid to be mixed 1506 is placed on the slide 1502. As a result, a small gas/vapor body 1508 forms with a gas/fluid interface 1510.
  • the body 1508 expands to become the bubble 1512.
  • the cyclic nature of the acoustic field 240 causes the bubble 1512 to cavitate.
  • applying and removing the acoustic filed 230 causes the bubble 912 to oscillate, thus providing a cyclic displacement of fluid adjacent to the interface 1510, and a local micromixing action in the fluid 1506 on the slide 1502.
  • One advantages of the mixing technology of the invention is that by locating or making use of cavitation features close to the edges or margins of the chamber of conduit, with the invention the highest fluid flow velocities are achieved at those locations. Other methods which provide bulk fluid flow cause the highest velocities to occur near the center of the chamber or conduit where they are less useful for applications such as flushing or reacting solution phase molecules with those bound to a surface.
  • Another advantage of the methodology of the invention is that mixing can be achieved in a rigid microdevice. Other technologies require that the chamber or conduit to be mixed have a flexible member (such as a plastic film contacting a liquid fluid or an aqueous/organic liquid fluid interface) that can be deflected by external means to cause bulk fluid motion within the device.
  • a further advantage of the invention is that nucleation sites or textures can be built into a microdevice such that mixing or fluid flow occurs only in desired locations. This is useful for controlling the extent and location of high velocity flows that may have a detrimental effect on sensitive areas within the device.
  • Another advantage of the invention is that it can operate either as an integrated component of a microdevice or as a separately fabricated, but acoustically coupled add-on.
  • the localized bubble formation and collapse created by the interaction of the acoustic field 240 with nucleation features can be employed to clean electrodes in a microdevice.
  • One of the difficulties of performing electrophoresis in a miniaturized format is the scaling effects of miniaturization.
  • Another difficulty is the presence of bubbles. Bubble- effects can block internal lumen, thereby rendering a sample/chip invalid.
  • Another limitation is the intrinsic properties of the electrophoresis process; namely, the generation of bubbles from the electrolysis of water at noble metal electrodes.
  • This bubble formation may have detrimental effects in miniaturized formats by blocking fluid flow, and by affecting the efficiency of the electrophoresis by limiting the current. Cleaning the electrodes can minimize some of these difficulties.
  • the invention may also be used to sweep across the electrophoresis zone to mechanically agitate the molecules to be separated.
  • FIGS 16A and 16B are conceptual block diagrams depicting a micro-electrode cleaning device according to an illustrative embodiment of the invention.
  • the microdevice 1602 is composed of two elements 1004 and 1006 arranged to form a chamber or conduit 1608.
  • the element 1604 includes a nucleation promoting feature 1610.
  • An electrode 1612 is mounted on the element 1606 and includes an electrically conductive lead 1614.
  • the chamber 1608 contains a liquid fluid.
  • An electrical current is applied via a connection 1706 to an electrode 1704 mounted on a substrate 1702 and in contact with a fluid medium 1708 such that hydrogen (or other gas) bubble(s) is generated.
  • Growth of the bubble may be either by continued generation of gas by electrolysis or by subsequent interaction with the acoustic field 240.
  • the bubble(s) will grow, release from the nucleation site and stream in response to gradients in the acoustic field.
  • the size of the electrolysis bubbles and the frequency of their occurrence can be controlled by the electrical signal to the electrode 1704. Many bubbles may be generated on an electrode 1704 or many individual electrodes 1704 or conductive sites may be employed.
  • Nucleation may be controlled by means of electrical signals applied to the sites rather than by an acoustical source. This method may be used to cause controlled nucleation of cavitation events at specific locations or in specific regions at specific times without the microdevice being movable relative to the acoustic source 230.
  • a device may have an integrated non-focused acoustic source 230. Bubble streaming and fluid flow can be activated in specific regions of the microdevice as required by controlled activation of electrodes 1704 in the regions.
  • Acoustic field gradients may be pre-established by the deployment of absorptive or reflective materials, either between the acoustic source 230 and the fluid volume 1708, or on the far side of the fluid volume 1708, relative to the acoustic source 230, so as to influence either incident or reflected acoustic radiation.
  • Figure 18 is a conceptual diagram depicting an acoustic based mixing apparatus that incorporates the acoustic source into a microfluidic device according to an illustrative embodiment of the invention.
  • Figure 18 shows a cross-section of a microfluidic device 1800 with an acoustic source 1890 which is connected to an electronic controller (not shown) by connections 1870 and 1880.
  • the device 1800 also includes nucleation promoting features 1850 which may be located in the microdevice opposite the acoustic source as shown or on the surface of the source itself.
  • the acoustic energy drives oscillation of a gas body or bubble 1810 in a fluid 1812 contained within a microchamber or microconduit formed by the two structures 1840 and 1845 provides a local micromixing action around the features 1850 indicated by the arrows 1820.
  • the acoustic source can also cause fluid motion by streaming of bubbles as shown in figure 13.
  • the acoustic source 1890 can form an entire internal surface of the microdevice, can form a portion of an internal surface of the microdevice or can be attached to an internal surface of the device.
  • the acoustic source 1890 can be integrally fabricated with the microdevice or may be separable from the microdevice so as to be reusable.
  • a thin film or membrane 1846 may separate the integrated acoustic source 1890 from the fluid 1812.
  • the membrane 1846 may be tailored to facilitate or block the transmission of the acoustic energy from the acoustic source 1890 into the fluid 1812 in selected areas.
  • the acoustic source 1890 may be any material or structure that emits acoustic energy such as but not limited to piezoelectric elements, magnetorestrictive elements, capacitive micromachined ultrasonic transducer (cMUT) elements and the like.
  • the acoustic source may be fabricated in situ as part of the microdevice by any manufacturing process such as but not limited to additive and subtractive processes performed in micro-electro mechanical systems (MEMS) fabrication or may be fabricated as a separate device and integrated into the microdevice in a subsequent manufacturing operation.
  • MEMS micro-electro mechanical systems
  • the acoustic waves generated by the source 230 can be any of a large variety of acoustic wavetrains characterized by being able to generate cavitation bubbles at nucleation sites of structural or material features at a power density below that needed to generate bubbles in non- featured regions.
  • An acoustic source can be unfocussed, or can have a line (one-dimensional focus), or can be focussed in two dimensions to a spot. In line and spot focus, there is also focus in the third dimension, which is usually controlled by the focus in the other dimensions.
  • Each of these focal modes is useful in particular embodiments of the invention. Spot focus is particularly useful for focussing on particular wells or spots in an array, such as the array 1102 of active sites 1104 of Figure 11.
  • Line focus can be used effectively to sweep an acoustic field across an array, thereby either simultaneously treating wells or spots, such as the detector sites 1104, by the row, or driving fluid through an array in a particular direction.
  • Non-focus (planar) waves are particularly effective for causing stirring or heating in the entire array (e.g., Figure 11), plate (e.g., Figure 15), or other object of treatment.
  • one of these modes is sufficient.
  • two or more may be needed.
  • the mixing apparatus has two sonic energy transducers/sources focused on two walls of a fluid containment vessel/microdevice.
  • the reagent chamber such as the chamber 1012 of Figure 10, volume is narrow to contain the fluid when the transducers are not activated.
  • the fluid is pumped out of the reagent chamber.
  • the transducers may be oriented such that planar standing waves form.
  • the transducers may be synchronized such that the deflection of the walls results in a maximum narrowing of the lumen or a maximal expansion of the lumen.
  • the mixing apparatus employs an unfocused acoustic energy source.
  • the field of textures may be very close to or a part of the transducer, such as a MEMS fabricated transducer with on-board nucleation site(s).
  • the energy input rate from the acoustic source is used to modulate the temperature of the fluid.
  • This benefits hybridization-based processes, and potentially other binding processes. Since the acoustic energy is able to provide mixing of the fluidic solutions surrounding solid-phase, immobilized binding partners, mismatches may be minimized. Adjusting the temperature during the process can also improve binding characteristics.
  • the mixing apparatus is used to mix a fluid in a miniaturized chamber.
  • One embodiment consists of a thick physical layer, a fluidic zone containing sample to be analyzed, and a thin physical layer. Materials that are appropriate for the physical layers include glass, polymers, and plastics.
  • the focused acoustic energy is directed to cavitate in the free fluid with the resultant shock wave impinging on the exterior of the device.
  • the impedance mismatches between the layers result in resonance of one of the layers. This compression-rarefaction vibration process induces mixing within the chamber. In a sense, the acoustic impedance mismatch drives an oscillating diaphragm.
  • the mixing apparatus is used to degas solutions. This may be useful for controlling dissolved gasses in a sample or reagent that is being loaded or has been loaded in a device.
  • the sample is loaded into a region of the microdevice that is in the focal point of the converged acoustic beam. Insonifying the region will prompt dissolved gas to be released prior to the sample entering the microfluidics.
  • the mixing apparatus of the invention is employed to facilitate or cause the aggregation and manipulation of small particles in small devices such as hybridization chambers that are used with DNA chips.
  • the mixing apparatus includes a source 230 for generating a focused acoustic field 240 that is arranged perpendicular to the plane of a hybridization chamber with a coupling medium (e.g., water) interposed.
  • the focal zone of the acoustic field 230 is positioned near or at the plane of the hybridization chamber.
  • the chamber can be moved relative to the acoustic field in the lateral or axial direction during or between treatments.
  • the mixing apparatus is configured such that the transducer faces upward in a water bath and the hybridization chamber is positioned horizontally at or near the surface of the water bath.
  • the air interface at the top side of the hybridization chamber forms an acoustically reflective surface that creates a standing-wave acoustic field within the microdevice.
  • the reflector may also be a metal plate or any other material that effectively reflects sound.
  • an ultrasound transducer operating at 1.1MHz produces a focal zone having an appropriate size and a gaussian intensity profile in the focal plane. Other frequencies may be used and other intensity profiles may be appropriate, such as a monotonic intensity gradient produced by an unfocused transducer operating at an oblique angle to the plane of the hybridization chamber or fluidic device.
  • the invention employs mixed frequencies to affect an acoustic field. For example, a brief tone burst at a high intensity at a high frequency to form acoustic bubbles may be followed by a tone burst at a lower frequency to retain the bubble(s) bolus and also soften the bubble collapse.
  • varying the frequency will also vary the focal zone location which may be beneficial for certain applications.
  • the acoustic 230 source has a cylindrical segment focused inward, such as a 45 degree arc of a cylinder to result in a line focal zone, e.g., about 1.5 mm wide x about 4 mm long x about 50 mm deep. If a microwell plate was swept across the focal zone line, an entire plate of small sample volumes such as the 1,536 wells of 1 microliter, may be rapidly treated.
  • a further application of the invention relates to histochemistry.
  • Histochemistry is the staining of tissue, particularly tissue sections and biopsies, for detection of diseases and other pathological states. It typically involves the sequential addition of numerous reagents to small samples for particular times, followed by washing out of the reagent and addition of a second reagent.
  • tissues may be dried, embedded, demineralized, and otherwise processed. Modern methods may involve specific labeling with protein or nucleic-acid based reagents.
  • the ability of the devices of the invention to provide gentle local stirring means that diffusional mixing in the liquid is no longer a limiting factor in the rate of processing. In some procedures, this could significantly decrease processing time.
  • the techniques of the invention allow remote control of fluid flow, which could simplify and help automate the techniques. Principles of the invention can be further understood through the following illustrative experimental examples. Example One: Cavitation Promoting Sites.
  • a glass slide was scratched with a diamond scribe.
  • the slide was placed in a slide holder and installed scratch-down in the apparatus of Figure 1, modified by the addition of a 5 MHz cavitation detection transducer placed confocally with the main 1.1 MHz acoustic power transducer 230.
  • This instrument was used for all the following examples except where noted.
  • a process was configured to sweep the slide through the focal point of the convergent acoustic beam of the power transducer.
  • the glass slide was insonified with a treatment waveform generated by a 100 mV, 1% duty cycle, 1000 cycles per burst signal applied to a 55 dB RF amplifier and input to the power transducer.
  • Both the input signal to the RF amplifier and the output signal from the cavitation detection transducer were applied to channels 1 and 2 of a Tektronix TDS 30334 digitizing oscilloscope.
  • the signal from the cavitation detection transducer was processed in real time to create a FFT frequency spectrum which was displayed on the oscilloscope screen along with the time-domain signals
  • Example 1 illustrates that the output signal from the cavitation detection transducer can be processed and one or more characteristics of the signal can be employed in a feedback control mechanism to control the intensity and nature (stable vs. transient) of the cavitation.
  • Example 1 also illustrates that stable and transient cavitation exhibit significantly distinct acoustic signatures that can be distinguished and differentiated by electronic or computer processing, and that surface features or textures promote cavitation.
  • Example Two Mixing with Particles in a Acoustic Field.
  • Example Three Selectively Blocking an Acoustic Field. If a microdevice or region to be treated is smaller than the focal region of a convergent acoustic beam, or if it is necessary to protect portions of the microdevice from the sound field, acoustic blocking materials may be placed to shadow selected areas from the acoustic source.
  • an acoustic blocking material (Tyvek) was applied to the outside of a chamber containing a piece of foil. The result was that cavitation damage preferentially occurs on the unblocked portion of the foil.
  • Example Four Cavitating Inside of a Chamber Without Cavitating on the Outside of the Device.
  • a chamber was constructed using a standard microscope slide for a base, a 1 mm thick by 25 mm square glass cover and laminated spacers along two edges.
  • the spacers each included a 10 micron thick Osmonics Poretics membrane (5 micron pore size) and a 37 micron polyester shim with the edges aligned inside the chamber, resulting in a 47 micron gap between the slide and the cover.
  • the chamber was clamped with small steel binder clips over each of the two spacers. The other two edges were left open. Acoustic energy was applied to the edge of the membrane/shim laminate by means of the apparatus of Figure 1.
  • a focused ultrasonic transducer (Sonic Concepts #H101) operating at a frequency of 1.1 MHz.
  • the slide was positioned horizontally at the surface of a water bath, coincident with the focal zone of the transducer.
  • the slide was held fixed in the vertical direction but movable in all horizontal directions.
  • the position of the slide is typically dithered in the horizontal plane during treatment to minimize the effects of misalignment of the slide relative to the transducer and to expose as many nucleation sites as possible along the edge of the membrane to the focal zone of the acoustic field.
  • Table 1 The voltage is the input voltage to a 55 dB RF amplifier.
  • the output of the amplifier was applied to the transducer through an impedance matching network.
  • the effective mixing distance from the edge of the chamber was forced to correlate with the acoustic power applied to the slide.
  • Higher power waveforms caused ink particles to move from one side of the chamber to the other, a distance of approximately 22 mm. Accelerating DNA Hybridization in an Open Chamber (Cover Slip).
  • the chamber described above was applied to a glass slide on the surface of which was spotted a DNA array of gene probes.
  • a target solution of cDNA in a hybridization buffer was applied to the chamber and incubated for 2 hours at 65° C while being treated with an acoustic field to promote mixing in the chamber.
  • a similar array was subjected to the same conditions without the acoustic treatment.
  • the treatment consisted of exposure to an acoustic waveform of 70 mV, 10%) duty cycle and 10 cycles per burst for approximately 5 minutes at 30 minute intervals. After treatment the two slides were post-processed together.
  • Example Six Non-contact Mixing in a Microliter Drop.
  • a one microliter drop of milk and India ink was applied to the dry surface of a glass slide at the water/air interface and in the focal zone of a 1.1 MHz focused transducer.
  • 0.5 microliter of milk was added to 0.5 microliter of India ink, the solutions slowly mixed, but when an acoustic wavetrain was applied to the drop, the two solutions rapidly mixed in less than 2 seconds.
  • the energy applied from the transducer to the drop had a peak positive pressure of approximately 3 MPa at 1% duty cycle with 1,000 cycles per burst.
  • a wavetrain was designed to have a short burst to nucleate and form a bubble or bubble cloud, followed by a lower amplitude period to allow the bubble(s) to slowly collapse, and followed by a period of no acoustic signal.
  • the following conditions worked well to both provide visual mixing in a dye filled chamber system and mix without disruption of immobilized DNA on polyLysine coated glass slides (i.e., following fluorescent dye staining), using the apparatus of Figure 1.
  • 10 cycles of 70 mV (amplifier input) followed by 2,500 cycles of 30 mV, and followed by 2,500 cycles of 0.1 mV.
  • This wavetrain was repeated and dithered across a field of scratches in a glass microscope cover slide with 0.5 mm spaces.
  • the dithering parameters were a 2 rpm rotational velocity and a 2 mm radius with a 0 second dwell time.
  • This wavetrain was scanned across the textured field.
  • the use of submicron particles of dye allowed visualization of controlled mixing. The observation was a smoother and less sporadic mixing than that observed without the step-down from the high intensity cycles.
  • a chamber with no features (or textures) containing water and milk was insonified .
  • Milk solids formed into a white spot at the center of the focal zone, surrounded by a clear ring. Milk solids were aggregated and segregated at the center of the focal zone. Dithering caused the white spot to smear out and remix.
  • Example Nine A hatch pattern was scratched into a glass slide with a diamond scribe and assembled as above. The result was that the milk solids did not form a spot. This seemed to be because either the scratches broke up the standing- wave field or the milk was being mixed faster than it could segregate.
  • Example Ten The previous experiment was repeated with ink added to the chamber to visualize mixing.
  • a 1 microliter drop of black ink (fountain pen ink) was added to the inside surface of the hybridization chamber and one or two drops of whole milk ere placed on the glass slide. When the two were brought into contact and clamped, the excess milk and some of the ink squeezed out, leaving the chamber filled with milk and a distinct smear of ink.
  • a "floating" cover slip was tested and compared to a gasketed chamber. This configuration seems to be more popular in the field of DNA microarray research.
  • a standard glass slide was cut down to 2" long for use as a cover slip.
  • a hatch pattern was scratched into the slide with a scratch interval of about 1 mm.
  • the slide was used as a cover slip because regular cover slips are too thin to scratch a pattern into. (A pattern could be etched into a standard cover slip, however).
  • a slide was set up in the slide holder and positioned in a Covaris El system with a -4 mm z offset.
  • a 1 microliter drop of white ink (Rotring #597118) was put onto the slide and the cover slip was applied, hatch side down.
  • Distilled water was wicked in to fill the gap between the slides. This caused a streak of ink between the slides.
  • a process was configured using 40 mV CW as the treatment. This caused excellent mixing in the chamber, especially when dithering was turned on. Example Fourteen.
  • Example Fifteen Field mixing with membrane bonded to cover slip. An Osmonics polycarbonate membrane with 5 micrometer pores was bonded to a 1 mm thick glass cover slip. The gap between the slide and the cover slip was set at 50 micrometers with plastic shims.
  • An array field may be constructed such that there are zones for nucleation and bubble collapse that act as pumps to stream fluid across the array. If the energy is high the resulting bubble collapse may disrupt bound binding partners. This may be a benefit to indicate in post- mixing scanning of the array that efficient mixing occurred.
  • the inclusion of various areas to indicate other aspects of the efficiency of the mixing may also be incorporated into the array. For example, areas that should have uniform amounts of dye may be dispersed across the array to indicate both mixing occurrence and efficiency.
  • the fluid flow was in the plane of the array and perpendicular to and originating from the membrane edges.
  • the flow was steady and was approximately 1 mm per second.
  • the flow pattern was from a point of approximately 1 mm and flowed over 10 mm perpendicular to the wall where the flow fanned out slightly to 3 mm. Adjusting the incoming voltages adjusted the velocity. Example Seventeen. Shelf or Ledge Mixing.
  • a ledge or shelf of exposed membrane material can be constructed at the edge of an array. This mixes in a mode similar to the above described field mixing but is positioned at the edge of the array. It has the advantage of creating a small gap in the mixing area (which requires less energy to activate) while allowing a larger gap over the array.
  • a 5 micron pore size Osmonics membrane was bonded to a shim such that a portion of the face of the membrane was exposed within the device. When treated with a "pulse-step" waveform having 10 cycles at 70 mV, 5000 cycles at 40 mV and no dead time, moderate mixing was observed within the chamber.
  • Example Eighteen Acoustic-based Temperature Cycling.
  • the temperature of a hybridization chamber may also be modulated by the rate at which the acoustic wavetrain enters the sample.
  • a glass microscope slide with a hybridization chamber was oriented horizontally a few millimeters above a water bath with an IR temperature sensor above the glass slide to monitor the temperature variation during the mixing dose. With a waveform of 10% duty cycle, 150 mV input to the amplifier, and a 100 cycles per burst the temperature went from 25°C to 60°C within 30 seconds. Thereafter, the temperature maintained a steady-state equilibrium condition.
  • modulating the acoustic wavetrain e.g., duty cycle
  • the temperature was raised or lowered. Controlling the temperature acoustically may be useful for accelerating stringency processes for hybridizations.
  • a small region of a device may be heated without heating other regions.
  • a target solution may be heated to denature it at the perimeter of an array without melting the hybridized molecules.
  • a chamber was constructed as follows: A laminate consisting of pressure sensitive silicone transfer adhesive applied to the top and bottom of an Osmonics Poretics polyester membrane having a 5 micron pore size and a 10 micron thickness, resulting in a total thickness of 60 microns was die-cut to form a chamber 21 mm square. The cut edge of the membrane was exposed. A cover layer of cyclic-olefin (Zeon Chemicals Zeonex 1600), 188 microns thick was punched to form two fill ports and applied to the membrane laminate to form a chamber. This chamber was bonded to a standard glass microscope slide. The volume of the chamber was approximately 40 microliters.
  • Ink was refined and prepared as above.
  • the chamber was filled with a mixture of the ink particles in IX SSC.
  • the ports were sealed with seal tabs (Grace Bio-Labs).
  • the chamber was placed cover-side down at the surface of the water bath in the sonic treatment system of Figure 1.
  • Acoustic energy was focused along the edges of the chamber such that the cut edge of the membrane was in the focal zone of the acoustic field.
  • a treatment waveform of 100 mV, 10 cycles per burst and 10% duty cycle was applied to the ultrasound transducer through a 55 dB RF amplifier to create an acoustic field focused on the slide.
  • the slide was robotically dithered in the horizontal plane during treatment so that focal zone moved in a circular pattern relative to the edge of the array to accommodate locational inaccuracies and to maximize the exposure of the edge of the membrane to the acoustic field.
  • the acoustic field applied to the edge of the laminate within the chamber resulted in circulating rotational flow of the fluid in "lobes" or eddies near the focal zone, as determined by visual observation.
  • This flow pattern was similar to that of a "doublet” as is known in the field of fluid dynamics.
  • the focal zone was robotically moved around the edge of the chamber (while dithering), a border of mixed fluid occurred within the chamber.
  • the treatment waveform described above resulted in border zone of mixed fluid having a width of approximately 5 mm.
  • the visually indicated border shows the region of primary circulation. Inside this border, the ink particles became organized into patterns formed by acoustic standing waves in the chamber and resisted moving with any fluid flow that may have occurred. Accelerating DNA Hybridization in a Closed Chamber.
  • a chamber similar to that described above was constructed and applied to a glass slide onto which was spotted a DNA probe array.
  • the chamber was filled with a target solution containing cDNA molecules in a hybridization buffer.
  • the slide was placed cover-side down at the surface of the water bath in the sonic treatment system of Figure 1 and treated with a treatment waveform of 100 mV, 10 cycles per burst and a 10% duty cycle for a period of 5 minutes at intervals of 30 minutes at an incubation temperature of 65° C.
  • a similar slide was prepared and subjected to the same conditions without the acoustic treatment. After the treatment period was completed the slides were post-processed and scanned. The slide receiving treatment showed substantially more fluorescent signal than the untreated slide.
  • Example Twenty Improved Signal From Mixing During Hybridization of a DNA Microarray, Nucleation Strip Applied Within a Closed Chamber.
  • the strip had a width of approximately 1 mm and a length of 8 mm.
  • the chamber was then applied to a glass slide onto which an array of two distinct DNA oligonucleotide probes had been spotted.
  • a similar chamber without the strip of laminate was also placed on the same slide.
  • a target solution of oligonucleotides complimentary to those spotted on the slide in a hybridization buffer was placed in both chambers.
  • the slide was placed upside down in the sonic treatment system of Figure 1 at the surface of the water bath at a temperature of 37° C.
  • the chamber with the strip of laminate was aligned with the focal zone of the ultrasound transducer and treated for 15 minutes with a waveform of 10 cycles of 125 mV, 10 cycles of
  • the slide was then post-processed and scanned with a slide scanner (Affymetrix #428).
  • the array in the treated chamber showed a substantially more uniform distribution of fluorescent signal across the array than the chamber that was not treated, by visual observation of the scanned image. The overall signal was higher too.
  • Example Twenty-One Mixing in a Chamber Using Unfocused Ultrasound.
  • a chamber having an internal size of 22 mm square by 60 microns high was placed on a slide that was spotted with a reference grid of fluorescent spots and an array of two distinct oligonucleotide probes.
  • the chamber was filled with 30 microliters of a target solution in which the target oligonucleotide molecules were complimentary to the spotted probes.
  • the slide and chamber were placed in a K&E Model 61-3128 ultrasonic pen cleaner filled with degassed water at room temperature.
  • the K&E pen cleaner was operated a voltage approximately 60% of line voltage (with a variac) which corresponds to a minimum value that reliably causes mixing as determined by visual and auditory means. After 15 minutes of treatment, the chamber was removed and the slide was post-processed and imaged.
  • a "nucleation patch" was bonded to a glass slide inside a standard hybridization chamber (Grace Bio-Labs #HBW1932)
  • the nucleation patch was in the configuration of a bandage in which a patch of membrane (Osmonics Poretics 10 micron pore size, 20 micron thick) was held down by a laminate of 25 microns of pressure sensitive adhesive and a 37 micron plastic film.
  • the dimensions of the membrane were 2 mm square and the overall dimensions were 2 mm X 6 mm.
  • the chamber was filled with refined white ink particles in IX SSC and placed chamber side down in the sonic treatment system of Figure 1.
  • the slide was insonified with a 100 mV, 10 cycles per burst, 10% duty cycle wavetrain.
  • Two chambers were constructed having an internal size of 9 mm X 12 mm X 150 microns high.
  • One chamber had Osmonics Poretics 5 micron pore size, 10 micron thick polyester membrane incorporated into the laminate.
  • the other chamber had plain polyester film, 12 microns thick instead of the membrane.
  • the chambers were laminated onto glass slides and filled with 30 microliters of solution containing sub-micron white TiO2 particles in IX SSC.
  • the slides were treated in the system of Figure 1.
  • a series of treatments was applied to the edge of each chamber.
  • the treatments had a voltage of 40 mV to 120 mV, increasing in increments of 10 mV.
  • the duty cycle was 10% and there were 10 cycles in each burst.
  • the presence of cavitation was noted and the extent of the mixing from the edge was recorded for each voltage in each chamber.
  • the series was repeated twice for each chamber. The extent of mixing was measured with digital calipers after 15 seconds of treatment at each voltage.
  • a chamber was constructed as follows: A laminate consisting of pressure sensitive silicone transfer adhesive applied to the top and bottom of an Osmonics Poretics polyester membrane having a 5 micron pore size and a 10 micron thickness, resulting in a total thickness of 60 microns was die-cut to form a chamber 21 mm square. The cut edge of the membrane was exposed. A cover layer of cyclic-olefin (Zeon Chemicals Zeonex 1600), 188 microns thick was punched to form two fill ports and applied to the membrane laminate to form a chamber. The chamber was modified as follows.
  • a strip of the silicone/membrane/silicone laminate measuring 1.5 mm by 6 mm was attached to the inside of the cover layer parallel to one of the edges so that a conduit 6 mm long was formed.
  • the conduit had a height of 60 microns and a width of approximately 1 mm. Both ends of the conduit were in free communication with the chamber.
  • the chamber was bonded then to a standard glass microscope slide. The volume of the chamber was approximately 35 microliters.
  • the chamber was filled with a mixture of refined ink particles in IX SSC and positioned in a Covaris El system.
  • An acoustic waveform of 80 mV amplitude, 10% duty cycle and 10 cycles per burst was applied to the chamber.
  • the chamber was positioned such that the focal zone was centered on one end of the conduit.

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Abstract

Selon l'invention, on utilise l'énergie acoustique pour réguler le mouvement d'un fluide. Dans un mode de réalisation, on dirige l'énergie acoustique au niveau d'éléments choisis favorisant une nucléation naturelle, de manière à réguler le mouvement d'un fluide. Dans un autre mode de réalisation, on apporte une énergie acoustique concentrée ou non au niveau d'éléments choisis favorisant une nucléation placée, de manière à réguler le mouvement du fluide. Dans une variante de réalisation, l'invention comprend une source acoustique, un module de commande destiné à commander le fonctionnement de la source acoustique, ainsi qu'un ou plusieurs éléments favorisant la nucléation et situés à proximité du fluide à réguler, ou dans ce fluide.
PCT/US2001/009163 2000-03-21 2001-03-21 Procede et dispositif de regulation acoustique de solutions liquides dans des dispositifs microfluidiques WO2001070381A2 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
CA002402985A CA2402985A1 (fr) 2000-03-21 2001-03-21 Procede et dispositif de regulation acoustique de solutions liquides dans des dispositifs microfluidiques
AU2001250929A AU2001250929A1 (en) 2000-03-21 2001-03-21 Method and apparatus for acoustically controlling liquid solutions in microfluidic devices

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WO2003079006A1 (fr) 2002-03-20 2003-09-25 Monica Almqvist Cellule microfluidique et procede de manipulation d'echantillon
US6814852B2 (en) 2002-07-15 2004-11-09 Hewlett-Packard Development Company, L.P. Generation of gas in a lab-on-a-chip environment
WO2005047882A3 (fr) * 2003-11-07 2005-10-20 Princeton Biochemicals Inc Appareil d'electrophorese multidimensionnelle
NL1026321C2 (nl) * 2004-06-03 2005-12-06 Univ Twente Inrichting en werkwijze voor het teweegbrengen van directioneel transport.
US7329388B2 (en) 1999-11-08 2008-02-12 Princeton Biochemicals, Inc. Electrophoresis apparatus having staggered passage configuration
US7736480B2 (en) 1999-11-08 2010-06-15 Princeton Biochemicals, Inc. Multi-dimensional electrophoresis method
US8007725B2 (en) 2003-11-07 2011-08-30 Princeton Biochemicals, Inc. Electrophoresis apparatus having valve system
US8110392B2 (en) 2006-06-23 2012-02-07 Micronics, Inc. Methods and devices for microfluidic point-of-care immunoassays
WO2013106458A2 (fr) 2012-01-09 2013-07-18 Micronics, Inc. Filière de réacteur microfluidique
US8921102B2 (en) 2005-07-29 2014-12-30 Gpb Scientific, Llc Devices and methods for enrichment and alteration of circulating tumor cells and other particles
US9056291B2 (en) 2005-11-30 2015-06-16 Micronics, Inc. Microfluidic reactor system
CN105008006A (zh) * 2013-02-11 2015-10-28 安德鲁·E·布洛什 用于提供非对称振荡的装置和方法
US9468894B2 (en) 2005-11-30 2016-10-18 Micronics, Inc. Microfluidic mixing and analytical apparatus
US9895692B2 (en) 2010-01-29 2018-02-20 Micronics, Inc. Sample-to-answer microfluidic cartridge
US10065186B2 (en) 2012-12-21 2018-09-04 Micronics, Inc. Fluidic circuits and related manufacturing methods
US10087440B2 (en) 2013-05-07 2018-10-02 Micronics, Inc. Device for preparation and analysis of nucleic acids
US10190153B2 (en) 2013-05-07 2019-01-29 Micronics, Inc. Methods for preparation of nucleic acid-containing samples using clay minerals and alkaline solutions
CN109821466A (zh) * 2019-01-09 2019-05-31 武汉智能装备工业技术研究院有限公司 一种多通道液体配料全自动调度系统及方法
US10386377B2 (en) 2013-05-07 2019-08-20 Micronics, Inc. Microfluidic devices and methods for performing serum separation and blood cross-matching
US10436713B2 (en) 2012-12-21 2019-10-08 Micronics, Inc. Portable fluorescence detection system and microassay cartridge
CN110536870A (zh) * 2016-12-02 2019-12-03 艾斯纽斯股份公司 流体处理系统及其使用方法
CN112632746A (zh) * 2020-11-23 2021-04-09 浙江大学 一种优化的土壤统计物理导热系数模型构建方法
US11179581B2 (en) 2015-03-09 2021-11-23 The Research Foundation For The State University Of New York Systems and methods for promoting cellular activities for tissue maintenance, repair, and regeneration
US11181105B2 (en) 2012-12-21 2021-11-23 Perkinelmer Health Sciences, Inc. Low elasticity films for microfluidic use
US11311686B2 (en) 2014-11-11 2022-04-26 The University Court Of The University Of Glasgow Surface acoustic wave device for the nebulisation of therapeutic liquids
WO2023039131A3 (fr) * 2021-09-10 2023-04-13 Elephas Biosciences Corporation Système et procédé de coupe de tissu

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US7736480B2 (en) 1999-11-08 2010-06-15 Princeton Biochemicals, Inc. Multi-dimensional electrophoresis method
US7811436B2 (en) 1999-11-08 2010-10-12 Princeton Biochemicals, Inc. Electrophoresis apparatus having an outlet passage
US7329388B2 (en) 1999-11-08 2008-02-12 Princeton Biochemicals, Inc. Electrophoresis apparatus having staggered passage configuration
WO2003079006A1 (fr) 2002-03-20 2003-09-25 Monica Almqvist Cellule microfluidique et procede de manipulation d'echantillon
US6814852B2 (en) 2002-07-15 2004-11-09 Hewlett-Packard Development Company, L.P. Generation of gas in a lab-on-a-chip environment
US8007724B2 (en) 2003-11-07 2011-08-30 Princeton Biochemicals, Inc. Electrophoresis apparatus having at least one auxiliary buffer passage
US8007725B2 (en) 2003-11-07 2011-08-30 Princeton Biochemicals, Inc. Electrophoresis apparatus having valve system
US8030092B2 (en) 2003-11-07 2011-10-04 Princeton Biochemicals, Inc. Controlled electrophoresis method
US8182746B2 (en) 2003-11-07 2012-05-22 Princeton Biochemicals, Inc. Electrophoresis process using a valve system
US8268247B2 (en) 2003-11-07 2012-09-18 Princeton Biochemicals, Inc. Electrophoresis extraction device
WO2005047882A3 (fr) * 2003-11-07 2005-10-20 Princeton Biochemicals Inc Appareil d'electrophorese multidimensionnelle
NL1026321C2 (nl) * 2004-06-03 2005-12-06 Univ Twente Inrichting en werkwijze voor het teweegbrengen van directioneel transport.
US8921102B2 (en) 2005-07-29 2014-12-30 Gpb Scientific, Llc Devices and methods for enrichment and alteration of circulating tumor cells and other particles
US9056291B2 (en) 2005-11-30 2015-06-16 Micronics, Inc. Microfluidic reactor system
US9468894B2 (en) 2005-11-30 2016-10-18 Micronics, Inc. Microfluidic mixing and analytical apparatus
US8110392B2 (en) 2006-06-23 2012-02-07 Micronics, Inc. Methods and devices for microfluidic point-of-care immunoassays
US9895692B2 (en) 2010-01-29 2018-02-20 Micronics, Inc. Sample-to-answer microfluidic cartridge
WO2013106458A2 (fr) 2012-01-09 2013-07-18 Micronics, Inc. Filière de réacteur microfluidique
US10436713B2 (en) 2012-12-21 2019-10-08 Micronics, Inc. Portable fluorescence detection system and microassay cartridge
US11181105B2 (en) 2012-12-21 2021-11-23 Perkinelmer Health Sciences, Inc. Low elasticity films for microfluidic use
US10065186B2 (en) 2012-12-21 2018-09-04 Micronics, Inc. Fluidic circuits and related manufacturing methods
CN105008006A (zh) * 2013-02-11 2015-10-28 安德鲁·E·布洛什 用于提供非对称振荡的装置和方法
US10087440B2 (en) 2013-05-07 2018-10-02 Micronics, Inc. Device for preparation and analysis of nucleic acids
US10190153B2 (en) 2013-05-07 2019-01-29 Micronics, Inc. Methods for preparation of nucleic acid-containing samples using clay minerals and alkaline solutions
US10386377B2 (en) 2013-05-07 2019-08-20 Micronics, Inc. Microfluidic devices and methods for performing serum separation and blood cross-matching
US11016108B2 (en) 2013-05-07 2021-05-25 Perkinelmer Health Sciences, Inc. Microfluidic devices and methods for performing serum separation and blood cross-matching
US11771846B2 (en) 2014-11-11 2023-10-03 The University Court Of The University Of Glasgow Nebulisation of liquids
US11311686B2 (en) 2014-11-11 2022-04-26 The University Court Of The University Of Glasgow Surface acoustic wave device for the nebulisation of therapeutic liquids
US11179581B2 (en) 2015-03-09 2021-11-23 The Research Foundation For The State University Of New York Systems and methods for promoting cellular activities for tissue maintenance, repair, and regeneration
CN110536870A (zh) * 2016-12-02 2019-12-03 艾斯纽斯股份公司 流体处理系统及其使用方法
CN109821466A (zh) * 2019-01-09 2019-05-31 武汉智能装备工业技术研究院有限公司 一种多通道液体配料全自动调度系统及方法
CN109821466B (zh) * 2019-01-09 2021-07-06 武汉智能装备工业技术研究院有限公司 一种多通道液体配料全自动调度系统及方法
CN112632746A (zh) * 2020-11-23 2021-04-09 浙江大学 一种优化的土壤统计物理导热系数模型构建方法
WO2023039131A3 (fr) * 2021-09-10 2023-04-13 Elephas Biosciences Corporation Système et procédé de coupe de tissu

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