WO1991000915A1 - Micro-injecteur a faisceau aerosol - Google Patents

Micro-injecteur a faisceau aerosol Download PDF

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Publication number
WO1991000915A1
WO1991000915A1 PCT/US1990/003663 US9003663W WO9100915A1 WO 1991000915 A1 WO1991000915 A1 WO 1991000915A1 US 9003663 W US9003663 W US 9003663W WO 9100915 A1 WO9100915 A1 WO 9100915A1
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particles
aerosol
cell
housing
conduit
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PCT/US1990/003663
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English (en)
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Laurens J. Mets
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Biotechnology Research & Development Corporation
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    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
    • C12N15/00—Mutation or genetic engineering; DNA or RNA concerning genetic engineering, vectors, e.g. plasmids, or their isolation, preparation or purification; Use of hosts therefor
    • C12N15/09—Recombinant DNA-technology
    • C12N15/87—Introduction of foreign genetic material using processes not otherwise provided for, e.g. co-transformation
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12M—APPARATUS FOR ENZYMOLOGY OR MICROBIOLOGY; APPARATUS FOR CULTURING MICROORGANISMS FOR PRODUCING BIOMASS, FOR GROWING CELLS OR FOR OBTAINING FERMENTATION OR METABOLIC PRODUCTS, i.e. BIOREACTORS OR FERMENTERS
    • C12M35/00—Means for application of stress for stimulating the growth of microorganisms or the generation of fermentation or metabolic products; Means for electroporation or cell fusion
    • C—CHEMISTRY; METALLURGY
    • C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
    • C12M—APPARATUS FOR ENZYMOLOGY OR MICROBIOLOGY; APPARATUS FOR CULTURING MICROORGANISMS FOR PRODUCING BIOMASS, FOR GROWING CELLS OR FOR OBTAINING FERMENTATION OR METABOLIC PRODUCTS, i.e. BIOREACTORS OR FERMENTERS
    • C12M35/00—Means for application of stress for stimulating the growth of microorganisms or the generation of fermentation or metabolic products; Means for electroporation or cell fusion
    • C12M35/04—Mechanical means, e.g. sonic waves, stretching forces, pressure or shear stimuli

Definitions

  • the present invention relates to the introduction of exogenous material into a living cell, tissue, or species, and more particularly, to apparatus and methods for microinjecting exogenous materials into a living cell, tissue, or species.
  • genetic transformation of cells using the technigues of genetic engineering has grown dramatically over the last few years.
  • genetic engineering involves the introduction of foreign DNA into a host cell to change or "transform" the host cell.
  • the genes carried by the foreign DNA are expressed in the host cell, and thus, the last cell is transformed.
  • hybridomas are the cell fusion product of antibody-secreting cells and "immortal" cells (myelomas) .
  • Hybridomas are used in medicine and research to produce monoclonal antibodies. Hybridomas, like the plant cell fusion products, may react unpredictably, and are expensive to produce and maintain.
  • Electroporation is another general method for introducing foreign DNA into cells. This procedure involves the exposure of a suspension of cells and fragments of foreign DNA to a pulsed high-voltage electrical discharge. This electrical discharge creates holes or pores in the cell membrane through which DNA fragments diffuse. Upon cessation of the electrical discharge, the pores in the cell membrane close, capturing any DNA fragments which have diffused into the cell.
  • a major drawback in using electroporation to introduce DNA into living cells is the necessity prior to a successful transformation, to determine empirically optimum values for a wide variety of parameters for each cell line in question. These parameters include voltage, capacitance, pulse time composition and resistance of electroporation medium, state of cell growth prior to electroporation, concentration of DNA, temperature, and cell density.
  • present methods for applying electroporation to cells with walls, such as plant cells require removing the walls prior to electroporation.
  • Viral infection is also an efficient means of transferring foreign DNA into some cells.
  • viruses are difficult to work with, and since a particular virus will only infect certain cells, the technique is not applicable to the broad spectrum of living cells, tissue, or species. Further, some virus may in fact be hazardous to the technicians working with them or to the environment.
  • the most common and effective method for transferring genes into plant cells involves conjugal transfer from living bacteria, primarily A ⁇ robacterium tumefacient and A ⁇ robacterium rhizocrenes.
  • the DNA to be transferred is first engineered into plasmids derived from the bacterial Ti plasmid, and the bacteria are then incubated in culture with the recipient plant cells.
  • the cultured, transformed cells must then be regenerated into genetically homogeneous plants. This method is limited to plants susceptible to Agrobacterium infection (principally dicots) that can be regenerated from cultures.
  • Still another technique for gene transfer is micropipette microinjection.
  • DNA or other exogenous materials are stably introduced into a living cell by microinjecting the material directing into the nuclei of the cell.
  • a glass micropipette having a diameter of from about 0.1 to about 0.5 microns is inserted directly into the nucleus of the cell.
  • the micropipette exogenous material such as DNA
  • An experienced, skilled technician can inject from about 500 to about 1000 cells per hour.
  • micropipette microinjection requires some fairly sophisticated and expensive equipment, such as, a micropipette puller for making the needles, and a micromanipulator to position the needles correctly for injection.
  • Micropipette microinjection is an effective method of gene transfer; however, because of the relatively small number of cells that may be transformed in any one experiment, the cost of the elaborate equipment necessary, and the level of skill needed to perform the procedure, microinjection using micropipettes is not a method of gene transfer available to the vast majority of researchers in the field.
  • FIG. l is a schematic illustration of the aerosol beam microinjector
  • Fig. 2 is a schematic illustration of an aerosol beam microinjector including a drying tube and means for providing sheath flow;
  • Fig. 3 is a schematic illustration of an aerosol beam microinjector additionally including means for adjusting the diameter of the injected droplet.
  • the present invention is directed to an apparatus an methods for the introduction of exogenous materials, for example foreign DNA, into a variety of recipient cells. It is believed that the present invention should have a profound effect upon the variety of plants, and animals, that will become amenable to direct genetic manipulation.
  • the present invention uses aerosol beam technology t accelerate either wet or dry aerosol particles to speeds enabling the particles to penetrate living cells upon impact therewith.
  • Aerosol particles suspended in a inert gas can be accelerated to a very high velocity during the jet expansion of the gas as it passes from a region of higher gas pressure to a region of lower gas pressure through a small orifice.
  • This acceleration process has been well-studied and used for many years in the field of aerosol physics.
  • the accelerated droplets may be positioned to impact a preferred target, for example, a plant or animal cell.
  • the particles include DNA or other macromolecules
  • the macromolecules are introduced into the cells.
  • the droplets may be constructed as droplets of a sufficiently small size so that the cells survive the penetration.
  • the macromolecules can elicit biological effects. This effect will depend on the specific properties of the macromolecules and the nature of the recipient cells. For example, DNA may be introduced into the target cell, thereby altering the genetic make-up of the cell. Because the method of introduction is a physical one, the biological barriers that restrict the application of other DNA transfer methods to a few plant species and a few cell types are not present. The size, kinetic energy and beam intensity of the aerosol stream can be precisely controlled over a wide range, and hence may be successful in penetrating and transforming a wide variety of cell types. In addition, the use of a continuous aerosol beam will permit the treatment of a large number of cells in the course of any single treatment.
  • the inventive method should be applicable to a wide range of plant species and cell types that have proved in the past to be quite impervious to standard methods of genetic engineering.
  • the apparatus and methods of the present invention are utilized tp produce a transformed line of plants. Aerosol particles ⁇ comprising exogenous genetic material are produced and accelerated to a speed enabling them to penetrate and enter into a living plant cell upon impact therewith. The cells are thereafter cultured to grow a plant. The progeny of the plant are subsequently screened using techniques well known to one skilled in the art of plant genetics, for transformed progeny.
  • the apparatus and methods of the present invention are utilized to produce transformed maize plants.
  • Cells from an embryogenic culture of an alcohol dehydrogenese-deficient (adh ⁇ ) recipient plant are preferably plated on an agar surface of osmotically supportive medium. They would then be placed in the chamber on the target positioning device for treatment with aerosol carrying a mild type ahd gene on a plasmid.
  • the apparatus shown in FIG. 3 is preferably used.
  • the DNA plasmid would be adjusted to 3mMMyCl 2 and rapidly mixed with 100% ethanol to yield 95% final ethanol concentration.
  • the concentration of DNA would be such that each droplet of primary aerosol generated in the nebulizer contains an average of 2-3 plasmid molecules (about 10 13 molecule per ml of final ethanol solutions) .
  • the primary aerosol, generated in the nebulizer would then be dried and the ethanol vapor trapped in the diffusion dryer.
  • the DNA aerosol stream would be humidified with 5x10 g water vapor per primary aerosol particles, and the mixture cooled to 0°c. to generate a 0.5 - 1.0 mm diameter uniform size aerosol droplets. These would be accelerated by the expansion of the N 2 inert gas through a 250 mm orifice to strike the target cells 1.5 cm away from the orifice.
  • the injected cells would then be cultured and tested by cytological staining for the presence of adh activity in the cells. An appropriate number of cells would be grown into plants and for the tested for the presence of the transforming DNA and for function of the adh gene.
  • a further preferred embodiment of the present invention utilizes the apparatus and methods of the present invention genetic transformation of maize pollen.
  • Pollen from a recipient variety deficient in adh would be plated on osmotically supportive agar medium and placed in the device shown in FIG. 3.
  • Transforming DNA would be formed into a primary aerosol of 95% ethanol as described for embryogenic cell transformation, and then dried as set forth above.
  • the aerosol stream would be humidified with perfluorocarbon vapor (3M or Air Products) at a density of 8xl0 ⁇ 12 g per primary aerosol droplet. Condensation at 0 ⁇ C would then generate 2 micron uniform diameter droplets. These would be accelerated with the inert gas expansion to impact the pollen grains.
  • the pollen After 1 hr recovery period, the pollen would be transferred to silks of adh deficient corn plants.
  • the seeds obtained would be planted and transformed plants recognized by the presence of adh-stainable pollen in samples from the mature plants.
  • Aerosol particles are formed by aerosolizing solutions containing the macromolecule. Preferably, excess solvent is subsequently evaporated from the aerosol particles to reduce projectile size, thus increasing the rate of survival in the impacted target cells.
  • the density of the final droplets is important, since less dense droplets may cause less damage to some target cells when they penetrate, while, on the other hand, more dense droplets may be required to penetrate certain target cells. Accordingly, the present invention provides means to modify both the size and density of the droplets as required for penetrating different cells. According to one preferred embodiment, the density of the droplets is from about 0.8 to about 8 gram/cc, and most preferably about 2 grams/cc.
  • the density is modified by the addition of solutes, for example colloidal gold, to the solution prior to forming an aerosol or by using solvents, such as perfluorocarbons, that have different densities.
  • the apparatus of the present invention may be modified to include means for removing excess solvent, thus reducing droplet size, or adding additional solvent to the droplet, thus increasing the size of the droplet.
  • Figs. 1, 2 and 3 illustrate several embodiments of an aerosol beam microinjector of the present invention. Each Fig. will be discussed in detail when appropriate, otherwise the following discussion is applicable to each FIG.
  • Compressed inert gas is filtered as it passes through a tubing 1 into the inlet 3 of a nebulizer 5 disbursing aerosol particles (a suspension of solvent and solute) into the inert gas to form an aerosol.
  • the source of the compressed gas 6 preferably provides a gas pressure of from about 10 to about 100 psi at the inlet 3.
  • the compressed gas most preferably provides about 30 psi at the inlet 3.
  • the projectiles droplets of solvent and suspended particulate matter
  • the projectiles have mass mean diameters of from about 0.1 to about 2 microns.
  • the present inventor has determined that projectiles having diameters outside of this range are not preferable in the practice of the present invention. Projectiles having a diameter of greater than about 2 microns were found to cause an unacceptable level of cell death following impact, while projectiles having a diameter of below about 0.1 microns were unable to efficiently penetrate into the target cell.
  • the aerosol exits the nebulizer 5 through an outlet 7.
  • the present inventor has determined that it is preferable to dissipate the pressure of the compressed gas prior to the acceleration of the aerosol. This is accomplished, in one preferred embodiment, by venting the aerosol to the outside atmosphere. As shown in Fig. 1, 2, and 3, the outlet 7 and the inlet 9 of tubing 11 do not abut each other, but are rather, positioned in a close proximity to each other. This arrangement allows the pressure of the compressed gas to dissipate, while furthe allowing the aerosol to enter inlet 9 of tubing 11. According to a further preferred embodiment not shown in the FIGS, the aerosol is discharged from the outlet 7 int -10-
  • a non-restrictive enclosure such as a non-reactive plastic bag.
  • a portion of the aerosol is drawn into the inlet 9 of a tubing 11.
  • the aerosol is drawn 5 into the tubing 11 by a negative or low gas pressure (a gas pressure below that of the surrounding atmosphere) .
  • This negative pressure is preferably about l atmosphere and is created within the tubing 11 by a high-volume vacuum pump 13 in communication with an air-tight vacuum
  • the inlet 9 of the tubing 11 is preferably positioned in a relatively close proximity to the nebulizer outlet 7. Preferably, this distance is
  • Fig. 1 shows the tubing 11 entering the housing 15.
  • Fig. 1 shows the tubing outlet 16 including a nozzle 17 through which the 20 inert gas and the aerosol eventually passes through to reach the vacuum housing 15.
  • the vacuum housing 15 may be regulated by the pumping speed of the pump 13, the flow resistance caused by the nozzle 17, or the evaporation of solvent from samples within the vacuum housing 15.
  • the aerosol is drawn through the length of tubing 11 to the nozzle 17.
  • nozzle 17 preferably has an aperture diameter of from 100 to 300 microns. The present inventor has determined that the most preferred aperture diameter of nozzle 17 is about 200 microns. The aerosol is thereafter drawn through nozzle 17 and into the vacuum housing 15.
  • the passage of the aerosol from the relatively high gas pressure area within tubing 11 into the relatively low gas pressure area within the vacuum housing 15 causes the inert gas to dramatically expand.
  • the rapid expansion of the inert gas through the nozzle 17 causes the aerosol particles to accelerate.
  • nitrogen is used as the inert gas
  • the aerosol particles can be accelerated up to speeds of from about 400 to about 800 meters/second.
  • helium is used as the inert gas
  • the aerosol particles may be accelerated up to speeds of about 2000 meters/second.
  • the vacuum housing 15 is continuously evacuated by the pump 13 to remove the inert gas and keep the pressure in the housing below the gas pressure in the tubing 11.
  • the gas pressure in housing 15 is from about 0.01 to about 0.05 atmospheres, and most preferably about 0.01 atmospheres.
  • Aerosol beams are thus composed of accelerated isolated particles and droplets (hereinafter referred to as simply projectiles) moving on well defined, straight line trajectories at speeds up to 2000 meters/seconds.
  • Fig. 2 illustrates an aerosol beam microinjector including means for manipulating the size of the projectiles, and means for focusing the aerosol flow through the nozzle 17.
  • a drying tube 23 contains a desiccant which traps solvent evaporated from the surface of the solute, thus decreasing the diameter of the projectile.
  • the drying tube 23 has an internal diameter of about one-half inch and an effective length of about 60 cm.
  • the drying tube 23 contains silica gel as a desiccant.
  • the silica gel surrounds a central channel formed by a cylinder of 20 mesh stainless steel screen.
  • Commercial drying tubes similar to the drying tube described above and useful in the practice of the present invention are available from TSI, Inc., Model 3062 Diffusion Dryer.
  • the aerosol is discharged from outlet 7 of tubing 11 and into the precise center of a laminar flow of dry, filtered inert gas.
  • the aerosol is thus entrained in the center of a gas stream moving up to and through the nozzle
  • 25 wall will have velocities substantially less than particles traveling in the center of the beam. Further, the radial expansion of the carrier gas will cause the aerosol beam to expand radially outward. Particles near the beam center are not influenced by this radial
  • Fig. 2 illustrates an aerosol beam microinjector which includes means for reducing the radial expansion of the aerosol beam and maintaining a substantially uniform velocity
  • Fig. 2 shows a piping 19 drawing filtered inert gas into its length and transporting that gas to the inlet 21 of the sheath flow piping 24.
  • the inert gas which accounts for the sheath flow, enters the piping 19 with no positive pressure and is drawn from a non-restrictive reservoir of inert gas or from the outside atmosphere when the inert gas is released from a source 26 in the immediate area of the inlet 25 of piping 19, as shown in Fig. 2.
  • the aerosol is discharged from tubing 11 into the center of the sheath flow piping 24.
  • the aerosol is entrained in the laminar flow of the inert gas in the sheath flow piping 24.
  • the laminar flow focuses the aerosol through the center of the nozzle 17, thus allowing the aerosol to maintain a substantially uniform velocity across its cross section.
  • the laminar flow also reduces beam spreading so that a more focused beam is obtained.
  • the laminar flow accounts for 50% of the flow through the nozzle 17.
  • Fig. 3 illustrates an aerosol beam microinjector having additional means to control particle size.
  • the apparatus of Fig. 3 includes a drying tube 23.
  • the drying tube removes substantially all the solvent from the aerosol.
  • the aerosol exiting the drying tube 23 through the tubing 11 is comprised substantially of dry solute.
  • the solute is discharged from the tubing 11 into a channel 27 of a gas reheater 29.
  • solvent saturated carrier gas is discharged into the channel 27.
  • the solvent saturated inert gas is produced in the vapor saturator 31 and is transported through the piping 19 to the channel 27 of the reheater 29. Filtered dry inert gas is drawn from a source 26 into the piping 19, a discussed for the apparatus of Fig. 2.
  • the inert gas thereafter enters the vapor saturator 31, wherein solvent vapor is added to the inert gas to the point of saturation.
  • the vapor saturator 31 is preferably constructed to contain solvent moistened fibrous material forming a central channel 33.
  • Surrounding the solvent- moistened material is preferably an aluminum block 28 heated to a desired temperature with resistive heaters 30. Preferably, this temperature is from about 50 to about 100° C.
  • the heat causes the solvent moistened material to release solvent vapor which is entrained by the inert gas.
  • solvent vapor which is entrained by the inert gas.
  • this is a preferred construction for the vapor saturator 31, other means to saturate the inert gas with solvent vapor may be utilized in the practice of the present invention.
  • the solvent-saturated inert gas is discharged from the vapor saturator 31 into piping 20 which communicates with channel 27 of the reheater 29.
  • the dry aerosol is discharged from tubing 11 also into the reheater 29.
  • the reheater 29 heats the dry aerosol and the solvent- saturated inert gas to a constant temperature. This facilitates the diffusion and mixing of the vapor- saturated inert gas and the dry aerosol particles.
  • the resulting mixture is heated to about 50 C.
  • the vapor condenser 35 is preferably constructed as having a central channel 37 wherein by reducing the temperature, the solvent vapor is condensed onto the aerosol particles. Depending on the temperature within the channel 37, the amount of solvent condensed may be controlled. Thus, the projectile size may be precisely controlled.
  • the vapor condenser 35 includes Lapeltier Coolers, obtained from Marlow Industries.
  • the vapor condenser outlet 39 includes the nozzle 17, and is positioned within the vacuum housing 15.
  • the target support platform 41 is a substantially horizontal surface capable of supporting target cells thereon and being preferably moveable along the X, Y and Z axis.
  • the target support platform 19 is provided with, supported by, and affixed to a motorized positioning member which enables it to be positioned either closer or farther away from the nozzle 17.
  • the target support platform 41 is preferably positioned about 1.5 cm from the nozzle 17.
  • this distance may be varied depending on the specific application. For example, it has been determined that the greater the distance the target support platform 41 is from the nozzle 17 the slower the impact speed of the projectiles.
  • the target support platform 41 is rotated and is moved by the positioning member along one linear axis 43. This allows for a biological sample placed on the target support platform 41 to be impacted throughout its entirety by projectiles.
  • the present inventors had determined that an effective rate of rotation about axis 43 is 40 rpm and that an effective rate of simultaneous linear advance along axis 43 is 333 microns per revolution. This allows the entirety of a biological sample of approximately 5x7 centimeters to be impacted (hereinafter referred to as scanned) in three to four minutes.
  • Preferable inert gases utilized in the practice of the present invention are filtered compressed inert gas.
  • a preferable carrier gas useful in the practice present invention is one gas selected from the group of gases consisting of carbon dioxide, room air, hydrogen, helium, and nitrogen.
  • the source of the carrier gas 6 is a source of gas capable of generating a gas pressure of 30 pounds per square inch at the inlet 3 of the nebulizer 7.
  • Preferred sources of compressed gas are compressed gas cylinder, and laboratory electrolytic cell gas generators.
  • the nebulizer 5 utilized in the practice of the present invention may be any nebulizer 5 which produces aerosols having droplet sizes of from 0.1 to about 3 microns in diameter.
  • ultrasonic nebulizers such as the LKB Instruments, model 108 may be used in the practice of the present invention, down draft or respiratory inhalation nebulizers of the Lovelace design are most preferred.
  • the most preferred nebulizers of the present invention is a nebulizer used in inhalation therapy obtained from Inhalation Plastic. Inc. , model 4207, of the Lovelace design.
  • These nebulizers are single use, disposable units that generate aerosol droplets with median mass diameters in the range of two microns. They require only a few millimeters of solution to operate efficiently and generate dense mist having up to droplets per liter of gas. Examples
  • Examples 1-3 are presented to demonstrate the optima range of particle sizes effective in transforming target cells in the practice of the present invention.
  • Examples 4-8 are presented to demonstrate the successful transformation of Chlamydomonas reinhardtii cells using the apparatus and methods of the present invention.
  • Ch1amydomonas reinhardtii is a unicellular eucaryoti green alga.
  • Cells of the wild type strain of Chlamydomonas reinhardtii (Chlamydomonas) were used as th target cells.
  • the cells were cultured in tris-acetate- phosphate (TAP) liquid medium. (Harris, E.H. Chlamydomonas Source Book. Academic Press, 1989) .
  • TAP tris-acetate- phosphate
  • the cells were concentrated by centrifugation and resuspended in TAP at a concentration of 10 7 cells/ml. 100 microliters of the cell suspension were subsequently plated onto an agar medium slab containing TAP and 1.5% b weight agar for consistency.
  • the slab also included an inert layer of Miracloth (Calbiochem, Co.) which was washed and steam autoclaved. Miracloth was included to facilitate the handling of the agar slabs.
  • the slabs were thereafter incubated at 25°C for from 1 to about 4 hours. Following the incubation period the slabs were chilled at 4°C for about an hour.
  • the schematic of the apparatus used in the instant example is shown in Fig. l.
  • the aerosol was produced by a respiratory therapy nebulizer, model 4207 obtained from Inhalation Plastic, Inc.
  • the mass median diameter of the aerosol droplets produced by the nebulizer was 2 micrometers, according to manufacturer's literature.
  • the nebulizing solution used was a buffered aqueous solution containing 0.01M sodium phosphate Ph 7.0 and 10 mg/ml of carboxyfluorescein. Both chemicals were obtained from the Sigma Chemical Company.
  • the carrying gas was compressed nitrogen having a flow rate of 4 liters/min to achieve 30 psi in the nebulizer.
  • the positive pressure created by the carrier gas was neutralized by opening the output piping of the nebulizer to the outside atmosphere.
  • the piping leading to the vacuum housing (tubing 11 in Fig. 1) was positioned in close proximity to the open outlet piping of the nebulizer.
  • the negative pressure in the system was created by a high-volume vacuum pump attached to the vacuum chamber.
  • the vacuum pump used was a Marvac model R-10, set at 170 liters/min.
  • the aerosol was accelerated into the vacuum housing through a nozzle having a diameter of 200 microns.
  • the agar slab on which the cells were plated was placed on the target support platform, which, in turn, was positioned 1.5cm from the nozzle.
  • the target support platform was rotated at 40 rpm, and advanced at a rate of 333 micrometers/revolution.
  • the entire slab was scanned (impacted by carrier gas or droplets) in about 3 to 4 minutes.
  • a control group of cells was created on the slab by interrupting the aerosol flow in a regular pattern. Thus, the control cells on the slab are impacted with only carrier gas.
  • the scanned slab was examined using a 4OX dissection microscope.
  • the slab was examined using a UV Products model T-33 longwave UV transilluminator.
  • the slab was placed on a petri dish containing TAP medium and incubated for 2 days.
  • th cells were removed from the slab, washed, resuspended in TAP liquid medium, and examined with a Nikon Labophot epifluorescence microscope, using a UV filter cube to observe carboxyfluorescein fluorescence.
  • Example 2 The protocol set forth in Example 1 was followed in Example 2 with the following exception.
  • a drying tube wa included in the apparatus. The drying tube was located i close proximity to the nebulizer, as shown in Fig. 2. Th drying tube had an internal diameter of 1/2 inch and was 60 cm long. It contained silica gel which surrounded a central channel formed by a cylinder of 20 mesh stainless steel screening.
  • the drying tube of the instant example was prepared by the inventor; however, similar drying tubes are available from TSI, Inc. (model 3062 Diffusion _ 20 _
  • Example 3 followed the protocol set forth in Example 1 with the following exceptions: the agar slab included
  • the target cells were wild type Chlamydomonas reinhardtii Mutant D15 which are incapable of growing on minimal media because of a deletion of the chloroplast tscA gene that renders them defective in photosynthesis. No spontaneous reversion of this deletion has been observed.
  • the DNA plasmid p71 used as the genetic transforming agent carries the Ch1amydomonas reinhardtii chloroplast DNA fragment Ecol ⁇ (Harris, E.H. Chlamydomona Source Book. Academic Press, 1989) cloned in J s , coli in the pUC8 cloning vector. It was obtained from Dr. Jane Aldrich, BP America. This fragment has the intact tscA gene that was deleted from the D15 mutant chloroplast DNA
  • the nebulizing solution included lO M tris-Cl pH 8.0 ImM disodium EDTA, 3mM magnesium chloride, O.lmg/ml plasmid p71, 10% polyethylene glycol 6000, and distilled water. All reagents were obtained from the Sigma Chemica Company. Polyethylene glycol and magnesium chloride are included in the solvent mixture to cause the tight condensation of the DNA, which protects it from shear degradation during aerosol formation. The effectiveness of this treatment was verified in preliminary experiments in which the aerosol generated from this solvent was recovered and the DNA analyzed by electrophoresis for intactness. In addition, it was tested for biological function by transformation of E_. coli.
  • the target cells were grown in TAP liquid medium and concentrated by centrifugation.
  • the cells were plated on an agar slab and incubated as described in Example 1. Before scanning, the agar slab was placed onto a petri plate containing solidified TAP medium containing 0.5M sorbitol for two hours at room temperature and for an additional one hour at 4 ⁇ C. It is believed that the presence of the sorbitol in the medium helps the cells to maintain their integrity during an osmotically sensitive period during recovery after being impacted by the projectiles.
  • Example 4 The apparatus used in Example 4 is illustrated schematically in Fig. 2.
  • the drying tube utilized was the same drying tube as used in Example 2.
  • the laminar flow accounted for 50% of the total flow through the nozzle.
  • the nozzle was 200 microns in diameter.
  • the target cells were positioned 1.5cm from the nozzle and the procedure used for scanning the surface of the agar slab was the same as was used in Examples 1-3.
  • the carrier gas was nitrogen and the flow rate through the drying tube was set at 160 ml/minute.
  • Ch1a vdomonas reinhardtii cells The cells were grown to
  • the aqueous phase separate from the second phenol extraction was mixed with one half volume of 7.5M ammonium acetate and then centrifuged in a micro centrifuge (Eppendorf) for one minute. The supernatant was thereafter mixed with two volumes of ethanol and placed in -70° C freezer for ten minutes. Th precipitated nucleic acids were collected by centrifugation in the micro centrifuge for one minute and the supernatant discarded. The pellet was resuspended in one tenth of TE buffer (lOmM tris-Cl, lmM disodium EDTA, pH 8.0). This ammonium acetate precipitation step was repeated once more.
  • TE buffer lOmM tris-Cl, lmM disodium EDTA, pH 8.0
  • the DNA obtained from the transfor ants was thereafter analyzed.
  • One aliquot of the DNA obtained as set forth above from one of transformants was digested with restriction enzyme EcoRI, one with a combination of BamHI and Bglll and one with Smal, using the enzymes according the manufacturer's instructions (Boehringer- Mannheim) .
  • EcoRI restriction enzyme
  • a similar digestion was performed on DNA from wild-type cells, DNA from the D15 mutant cells, and DNA from the p71 plasmid used in the transformation experiment.
  • the DNA fragments were separated by electrophoresis in 0.7% agarose gels using tris-borate- EDTA buffer according to standard procedures.
  • the DNA was transferred to Nytran membranes (Schleicher and Schuell) using the standard Southern blot procedure.
  • Probes were prepared from pUC18 plasmid DNA and from fragments of the Eco-18 chloroplast DNA isolated from the p71 plasmid.

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  • Medicinal Preparation (AREA)
  • Medicines That Contain Protein Lipid Enzymes And Other Medicines (AREA)

Abstract

L'invention concerne la technologie à faisceau aérosol en vue d'accélérer des particules aérosol mouillées ou sèches pour leur conférer des vitesses leur permettant de pénétrer dans des cellules vivantes. Des particules aérosol en suspension dans un gaz inerte sont accélérées jusqu'à atteindre une vitesse très élevée pendant l'expansion du jet de gaz lorsqu'il passe d'une région de pression de gaz élevée vers une région de pression de gaz basse au travers d'un petit orifice. Les particules accélérées sont positionnées pour heurter une cible préférée, par exemple une culture bactérienne ou cellulaire végétale ou animale. Lorsque les gouttelettes contiennent de l'ADN ou d'autres macromolécules, ces macromolécules sont introduites dans les cellules. Les particules sont construites sous forme de gouttelettes d'une taille suffisamment petite pour que les cellules survivent à la pénétration. Une fois introduites dans la cellule cible, les macromolécules peuvent y exercer des effets biologiques. Etant donné que le procédé d'introduction est un procédé physique, les barrières biologiques qui restreignent l'application d'autres procédés de transfert d'ADN sur quelques espèces végétales et quelques types de cellules ne sont pas présentes. De plus, le procédé et l'appareil de la présente invention permettent le traitement d'un grand nombre de cellules lors d'un seul traitement. Ainsi, le procédé et l'appareil de l'invention devraient s'appliquer à une grande variété d'espèces végétales et de types de cellules qui se sont révélés par le passé peu propices aux méthodes standard de génie génétique.
PCT/US1990/003663 1989-07-11 1990-06-27 Micro-injecteur a faisceau aerosol WO1991000915A1 (fr)

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US37825689A 1989-07-11 1989-07-11
US378,256 1989-07-11

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WO1991000915A1 true WO1991000915A1 (fr) 1991-01-24

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EP (1) EP0482125A1 (fr)
AU (1) AU642889B2 (fr)
IE (1) IE61705B1 (fr)
WO (1) WO1991000915A1 (fr)

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EP0531506A1 (fr) * 1991-03-06 1993-03-17 Agracetus, Inc. Transformation du coton induite par des particules
WO1993007256A1 (fr) * 1991-10-07 1993-04-15 Ciba-Geigy Ag Canon a particules pour introduire de l'adn dans des cellules intactes
WO1993023552A1 (fr) * 1992-05-21 1993-11-25 Government Of The United States As Represented By Secretary Department Of Health And Human Services Ciblage de l'expression genique sur des tissus vivants par injection a jet
WO1995033061A1 (fr) * 1994-05-31 1995-12-07 Boehringer Ingelheim International Gmbh Procede d'introduction d'acide nucleique dans des cellules eucaryotes d'ordre superieur
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WO1993007256A1 (fr) * 1991-10-07 1993-04-15 Ciba-Geigy Ag Canon a particules pour introduire de l'adn dans des cellules intactes
US5998382A (en) * 1992-05-21 1999-12-07 The United States Of America As Represented By The Department Of Health And Human Services Targeting gene expression to living tissue using jet injection
WO1993023552A1 (fr) * 1992-05-21 1993-11-25 Government Of The United States As Represented By Secretary Department Of Health And Human Services Ciblage de l'expression genique sur des tissus vivants par injection a jet
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IE61705B1 (en) 1994-11-30
IE902504A1 (en) 1991-03-13
EP0482125A1 (fr) 1992-04-29
AU5950090A (en) 1991-02-06

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