|Publication number||US3424154 A|
|Publication date||Jan 28, 1969|
|Filing date||Nov 8, 1965|
|Priority date||Nov 8, 1965|
|Publication number||US 3424154 A, US 3424154A, US-A-3424154, US3424154 A, US3424154A|
|Inventors||Kinsley Charles W|
|Original Assignee||Kinsley Charles W|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (8), Referenced by (123), Classifications (9)|
|External Links: USPTO, USPTO Assignment, Espacenet|
Jan. 28, 1969 c. w. KINSLEY INJECTION SYSTEM Sheet of 2 Filed Nov. 8, 1965 f INVENTOR. B/HARLES W. KlNsLEY E427 izq/28 Jan. 28, 1969 c. w. KlNsLl-:Y 3,424,154
INJECTION SYSTEM Filed Nov. 8, 1965 sheet 2 of 2 United States Patent O Claims ABSTRACT OF THE DISCLOSURE A system for injecting liuids, such as local anesthetic liquids, into the soft tissues, particularly the gums, of a living body comprising a hand piece having a probe terminating in a jet orifice from which a high-velocity jet of liquid may be ejected from an ampule within the hand piece by movement of a piston within the hand piece and actuated by a liquid column in a ilexible tube connected to a remote pneumatic motor. In the preferred form, the pneumatic motor includes a major piston and an auxiliary piston spring urged away from said major piston but movable, under the inlluence of pressure flow, to strike a hammer blow against said major piston in the direction of liquid-ejecting motion of said major piston, to start said major piston in such motion.
The present invention relates to a system for injecting fluids into the soft tissues of a living body without the use of a solid instrument for puncturing the skin. The principle of this type of injection has been in use for several years and its effectiveness for the hypodermic placement of anesthetics, medicaments and the like is recognized. However, apparatus for accomplishment such injection,
which is usually referred to as jet injection has heretofore been heavy, cumbersome, difficult to apply in restricted regions, expensive to produce and not well adapted to maintenance in reasonably sterile condition.
Because of the awkwardness of previously known apparatus, and because of other characteristics thereof, the principle of jet injection has not been applied to dental anesthesia, so far as I know, except in one series of experiments conducted under the Iauspices of the United States Armed Forces and reported in the United States Armed Forces Medical Journal, volume IX No. 5, dated May 1958. In that series of experiments, the basic principlesof previously-known apparatus for jet injection were used, the only signicant modification being the provision of an elongated and bent probe attached to the main housing of such known apparatus. So far as I am advised, although those experiments were reasonably successful, they have not since been extended and the principle of jet injection has not been adopted at all by the dental profession.
Among the disadvantages of previously-known apparatus for jet injection is the fact that such apparatus has universally depended upon heavy springs, pre-stressed by suitable winding means and trigger-released, to drive piston means for applying pressure and motive force to eject a fluid, through a restricted orifice, to accomplish the injection. Inevitably, when the spring-driven piston reachesthe end of its stroke in such apparatus, at least a slight mechanical blow is delivered to the body of the apparatus; and since the apparatus is necessarily in contact with the patient, the patient will feel some physical shock. If the site of the injection is a patients jaw, even a slight mechanical shock is highly objectionable. The fall of the piston also necessarily produces some noise; and, again, if A'the apparatus is in contact with the patients jaw, that noise will be exaggerated in the patients hearing.
Among the objects of the present invention is the provision of jet injection apparatus in which motive force is 3,424,154 Patented Jan. 28, 1969 lCe applied to the fluid for injection through iluid motor means, in which the probe, the medicament-contalnmg ampule and the piston directly associated with the ampule may be assembled in a small, light, readily-manipulable housing and that housing may be physically remote from the prime mover through which power is applied to the said piston. In its optimum form, the above mentioned assembly will be operatively connected to the prime mover through a flexible tube in which is contained a liquid column through which motion of the prime mover is transmitted to the piston element of the said assembly.
A further object of the invention is to provide apparatus of the character described in which all of the apparatus except the small, above mentioned 'assembly may be screened from the vision of the patient. A still further object of the invention is to provide such apparatus in which the prime mover will not deliver a physical shock to the hand-held assembly, in which the noise resulting from operation of the prime mover will not ibe transmitted to the hand-held unit and in which the patient will not be subjected either to physical shock or to exaggerated noise transmitted to his cranial bone structure through the probe Another object of the invention is to provide jet injection apparatus which is devoid of springs, which is simple and inexpensive in construction and in which the portions which must be brought into close contiguity to the patient may be readily dismounted for easy sterilization.
Still another object of the invention is to provide a novel ampule for containing the fluid to be injected, the particular construction of said ampule adapting it for highly advantageous use in the apparatus herein disclosed.
Still further objects of the invention will appear as the description proceeds.
To the accomplishment of the above and related 0bjects, my invention may be embodied in the forms illustrated in the `accompanying drawings, attention being called to the fact, however, that Vthe drawings are illustrative only, 'and that change may be made in the specilic constructions illustrated and described, so long as the scope of the appended claims is not violated.
FIG. 1 is a more or less diagrammatic illustration of a system embodying the present invention;
FIG. 2 is an enlarged, longitudinal section through a portion of the hand-held assembly forming a feature of the invention, and illustrating a novel ampule in place for use in the system;
FIG. 3 is a further-enlarged, fragmentary section illustrating details of construction of the distal end portion of la probe constituting an element of the invention, shown in use position and illustrating the mode of cooperation of the probe end with the soft tissues of the patient, in a somewhat idealized form;
FIG. 4 is an enlarged, axial section through the lluid motor constituting the prime mover of the system of the present invention; and
FIG. 5 is a section of the distal end portion of a modilied form of probe.
Referring more particularly to the drawings, it will be seen that I have illustrated a tubular body 10, open at both ends and formed Iat one end with a reduced, externally threaded extension 11. A tubular probe is indicated generally by the reference numeral 12 and comprises a shank or distal portion 13 and an enlarged base 14 formed at its proximal end with a socket 15 having an internally threaded extension 16 for cooperative engagement with the extension 11 of the body 10. The probe is formed with an axial bore 17 in which is received, with an easy push iit, a hollow tube 18.
Advantageously, the hollow tube 18 maybe essentially a conventional hypodermic needle whose Ibore 19 is of the desired diameter, but whose unsharpened end has been spun down or tapered as at 20 to define a minute orifice 21. Such a needle is conventionally provided with a fixed bead 22 and the socket 15 is desirably formed with a seat 23 against which the bead 22 abuts to limit movement of the tube toward the distal end of the probe shank 13. It will be perceived that, when the bead is so seated, the sharpened end 24 of the needle '18 is disposed within the socket 15 at a predetermined axial position and for a reason which will appear.
An ampule for use in the assembly is indicated generally by the reference numeral 25. It comprises a body 26 proportioned and designed for snug reception in the tubular body 10, and a neck 27 of reduced diameter adapted to extend beyond the open end of the reduced extension 11. The neck 27 is closed by a penetrable diaphragm 28, such as a rubberoid stopper, held in place by a preferably metal collar 29 externally gripping the neck of the ampule and centrally formed with a perforation 30. It will be readily perceived that, when the ampule is positioned in the body 1()` and when the probe base 14 is moved by the coaction of the threads 11 and 16 to bring the socket 15 into communicating registry with the open end of the body 10, the sharpened end 24 of the needle '18 will penetrate the diaphragm 28 to enter the interior of the ampule and the base of the socket 1S will bear upon the collar 29 to hold the ampule positively against movement toward the left as viewed in FIG. 2.
The opposite end of the ampule is closed by a stopper 31 which is designed and intended to act as a piston Within the ampule, movable toward the left to eject the contents of the ampule through the needle 18. The piston 31 is formed of material which is resiliently transaxially compressible, and its equilibrium diameter somewhat exceeds the internal diameter of the ampule body 26. Preferably, the forward or distal end of the piston 31 is formed with a reduced extension 34 whose diameter is slightly less than the internal diameter of the ampule neck 27, and that extension is circumscribed by an annular groove 35 defining a forwardly-tapered annular lip 36. The piston 31 is inserted in the rear end of the ampule by peripherally contracting the lip 36, entering the lip in the ampule end, and then forcing the piston toward the left, as viewed in FIG. 2, until the major portion of the length of the piston is enclosed Within the ampule body, but a minor portion 32 of the pistons length remains outside the ampule body. As the piston is so entered in the ampule body, of course it will be transaxially compressed, while the portion 32 will retain its equilibrium diameter. As a consequence, when the piston reaches its illustrated position relative to the ampule body, its proximal end portion 32 will define a peripheral lip 33 overhanging the proximal end of the ampule body; and that lip will offer a significant degree of resistance to further movement of the piston 31 toward the left relative to the ampule body.
A piston 37, having an elongated stem or plunger 38, is reciprocably mounted in the tubular body behind the ampule 25, said stem preferably being guided in an annular bearing 39 within the length of the body 10, and the body being provided with one or more vent ports 40 just to the rear of said shoulder so that pressure cannot build up within the body between the head of the piston 37 and the ampule 25. As is most clearly illustrated in FIG. 2, the distal end of plunger 38 has a diameter slightly smaller than the internal diameter of the ampule body 26, and is constructed and arranged to bear atly against the proximal end of the piston 31.
Suitable coupling means 41 connects the open proximal end of the body 10 through a iiexible tube 42 to a T-fitting 43 which, in turn, is connected by conduit means 44 to an elongated chamber 45. The chamber 45, as shown, is formed with an annular, internal step or shoulder 46 upon which is supported a liner 47, suitable packing means 48 being carried between the liner and the shoulder 46. A third piston 49 is reciprocably received in the liner 47.
Suitable coupling means 50 connects the upper end of the chamber 45 with the bottom head 51 of a pneumatic motor indicated generally by the reference numeral 52. An open ended cylinder 53 has one end closed by the head 51 and has its other end closed by an upper head 54 to define a chamber 55 which is entered by the stem 56 of the piston 49; and within said chamber 55, said stern carries a fourth piston 57 which is penetrated by one or more axially extending ports 58 and which is much larger in effective diameter than the pistons 49 and 37. A headed guide pin 59 is fixed to said fourth piston 57 and limits the path of travel, relative to the piston 57, of a fifth piston 60, a coiled spring 61 being confined between the pistons 57 and 60 to urge the piston 60 away from the piston 57.
The head 51 is formed with a port 62 to Which is connected a branch pipe 63, and the head 54 is formed With a port -64 to which is connected a branch pipe 65 for purposes which will appear.
In FIG. 4, the assembly comprising the pistons 49, 57 and 60, the stem 56 and the pin 59, is shown in its normal, retracted position, with the pistons 60 and 57 fully separated. The cylinder 53 is formed with a port 66 at a level which, when the said assembly is so retracted, registers with the space between the pistons 57 and 66. The reduced neck 67 of a valve housing 68 is threadedly received in the port 66. Said housing is formed to provide an internal seat 69 with which cooperates a valve member 70 yieldably held in closing contact with said seat by a coiled spring 71 confined between said valve member and an adjustable screw 72 threadedly received in that end of the housing 68 remote from the neck 67. It will be apparent that adjustment of the screw 72 will vary the effective force with which the spring 71 urges the valve member against the seat 69. A jam nut 73 may be provided to retain the screw 72 in any selected position of adjustment. An exhaust port 74 opens from the interior of the housing 68 to atmosphere.
A conduit 75 leads from a source (not shown) of air under pressure to a T-fitting 76 with which is connected an accumulator chamber 77, a pressure gauge 77' being in communication with said chamber. A pipe 78 leads from the fitting 76 to the inlet port 79 of a conventional four-Way valve 80 having one delivery port 81 to which is connected the branch pipe 63 and a second delivery port I82 to which is connected the branch pipe 65. To the exhaust port 83 of the valve 80 is preferably connected a pipe 85 leading to a muier 86. Conventional solenoid programming means for the valve 80 is indicated at 84.
From the T-litting 43 extends a pipe 87 with which communicates a pressure gauge 88, and said pipe leads, through a check valve 89, to a manually-operable pump connected to a liquid reservoir 91. The pump 90 is operable to establish a continuous column of liquid within the tube 42, the tubular body 10 and the elongated chamber 45, providing an airmative motion-transmitting link between the piston 49 and the piston 37; and it will be seen that said pump is further operable to establish a predetermined degree of pressure within said column.
In FIG. 3, I have illustrated what I presently consider to be an optimum form for the distal end face 92 of the probe 13. As shown, said end face 92 is formed with a central, outwardly flaring cavity 93 within which is disposed the tip of the needle 18 defining the jet orifice 21, said tip being substantially flush with the transaxial surface 92. The cavity 93 is circumscribed by an annular groove 94. Thus, when the probe face 92 is pressed against a region 95 of the soft tissues of a living body, it tends to establish a mound 96 protruding into the cavity 93 and centrally depressed by the tip 20 of the needle; and it tends to establish, as well, an annular mound 97 surrounding the mound 96. Thus, substantial normality of the axis of the tip region of the needle 18 relative to the surface of the tissues engaged by the needle tip is assured; and this is important because it has been discovered that unless such normality is maintained, the issuing jet of liquid is likely to lacerate the tissues instead of establishing the desired rectilinear channel within the tissues.
In FIG. 5, I have illustrated a fragment of a modified form of probe 12 in which the shank 13' is bent to facilitate the location of its tip 92' in a restricted region. Needles 18 of the character above described are quite flexible, and I have found that a needle 18 can `be inserted in the bore 17 of such a probe without difficulty.
It is known that, for optimum practice of jet injection,
the initial portion of the jet stream, which is to accomplish the drilling, tissue-penetration or opening of a channel to a desired depth beneath the skin must be moving at extremely high velocity, and therefore under maximum pressure. This penetrating stream should be followed by an abrupt pressure decay to a much lower velocity whereby the following liquid may flow into the channel so defined and may disperse radially through the tissue layers, primarily near the bottom of the channel which has thus been prepared by the initial pressure stream. As the injection nears completion, the pressure and velocity of the stream should again drop sharply to zero. While quantitative pressure and velocity values cannot be specically prescribed, it can be said that, in most cases, the pressure program which starts at zero p.s.i. should climb almost instantaneously to a maximum of, for instance, 8000 p.s.i. for drilling, should then fall off steeply to perhaps 3,000 p.s.i. for injection and dispersal of the main charge and then should fall off steeply to zero p.s.i. at the end of the injection cycle.
In an apparatus of the character here under consideration, pressure and velocity through a given orifice bear a direct relationship to each other and therefore it can be seen that regulation of the pressure which is brought to bear on the injection iiuid (upstream from the orifice) will determine the velocity of injection and thus the depth of the channel and the amount of dispersal of the following liquid charge. The apparatus herein disclosed inherently will operate to accomplish the pressure program above described as optimum.
Operation The apparatus is designed primarily for use with forty pound air pressure which is available in most dental offices and in the offices of many physicians; but of course it will be understood that, by adaptations which will be obvious to those skilled in the art, the Huid motor 52 could be supplied from pressure cylinders or in any other way. When the apparatus is to be used, the probe 12 will be removed from the tubular body and an ampule 25 containing the proper volume of the fluid to be injected will be inserted through the thus-opened end of the tubular body 10. The ampule is so proportioned and designed that, when its piston 31 is pressed against the distal end of the retracted piston stem 38, the ampule neck will project beyond the open end of the body 10. Now, the probe 12 is mounted on the body 10 by threading the extensions 16 and 11 together, and as the extension 16 approaches its seat, the sharpened end 24 of the needle 18 will pass through the port 30 in the collar 29 and will penetrate the diaphragm 28, thus opening the interior of the needle 18 to the contents of the ampule 25.
The column of liquid between the pistons 49 and 37, once established, will normally be maintained at all times. Just before the apparatus is to be used, the plunger of the pump 90 will be depressed a few times in order to prepressurize that column or hydraulic link to approximately 1 to 2 p.s.i. as indicated on the gauge 88 in order to be certain that the hydraulic link is solid throughout the system so that the movement of the piston 37 shall certainly be directly proportional to the movement of the piston 57. The lip 33 of the piston 31 provides sufficient resistance to leftward movement of the piston to retain aid piston against such pre-pressurizaiton of the hydraulic ink.
The normal or rest condition of the valve is such as to retain the piston assembly 57-60 in its illustrated position. The operator now places the distal face 92 of the probe 12 or 12 in proper position against the tissue to be injected, and trips a trigger (not shown) which actuates the control 84 to dump compressed air from the accumulator tank 77 through the branch pipe 65 into the upper end of the cylinder 53. Instantly, the fifth piston 60 is forced downward with an accelerating velocity, against the tendency of the spring 61, toward the upper face of the fourth piston 57. Air entrapped between the pistons 60 and 57, of course, ows freely through the ports 58 and thence through the branch pipe 63 to be discharged through the exhaust pipe 85. By the time the piston 60 comes into contact with the piston 57, the piston 60 is moving at high velocity and its mass transmits a heavy initial hammer blow to the piston 57. If desired, the contacting surfaces of the pistons 60 and 57 may be cushioned with a nylon or Teflon pad to reduce the noise of contact. The hammer blow, of course, moves the piston 49 instantaneously, but through a very short distance, at extremely high velocity; and movement of the piston 49, of course, is transmitted through the -hydraulic link to the piston 37 and thence to the piston 31 so that a jet of the fluid contained in the ampule 25 will be emitted at extremely high velocity through the minute orifice 21 to drill the desired channel in the tissues 95.
If, for instance, the effective area of the pistons 60` and 57 has a two inch diameter while the pistons 49 and 38 have one-quarter inch diameters, a pressure of 40 p.s.i. on the pistons 60 and 57 will be multiplied to approximately 8000 p.s.i. delivered to the piston 31; and of course the initial starting pressure exerted on the piston 31 will be considerably higher than that because of the inertial effect of the impact of the piston 60 upon the piston 57.
After the piston 60 has thus delivered its hammer blow to the piston 57, the two pistons will continue to move downwardly to force following portions of the contents of the ampule 25 to enter the channel defined in the soft tissues. Momentarily thereafter, the upper end of the piston 60 will clear the port 66 whereby a metered escape of a portion of the incoming air past the valve 70 will be established to assist in reducing the velocity of travel of the piston assembly, thus controlling the rate of decay of the velocity of discharge of the contents of the ampule.
During travel of the piston 31, of course, the lip 36 is forcibly pressed against the internal wall of the ampule to inhibit escape of the uid past the piston. The provision of the reduced extension 34, which will enter the ampule neck 27 at the end of the piston stroke, provides for maximum use of the contents of the ampule. It is not intended, however, that the extension 34 shall have a uid tight fit in the ampule neck; and the lip 36 will engage the shoulder of the ampule at the base of the neck to stop piston movement before the extension 34 can come into contact with the sharpened end 24 of the needle 18.
Preferably, the control 84 for the valve 80 will be of such -character that, upon completion of the stroke of the piston 31, the valve 80 will be actuated to connect the pressure supply to the branch pipe 63 and connect the branch pipe 65 to exhaust, whereby the pistons 57 and 60 will be lifted. Such movement, of course, will be accompanied by retraction of the piston 37, whereupon the probe 12 may be disconnected from the body 10, the ex- -hausted a-mpule may be removed and a new ampule may be inserted if the mechanism is to be promptly used again.
I claim as my invention:
1. A system for injecting fluids into the soft tissues of a living body, said system comprising a tubular body provided at one end with a probe formed with an axial orifice, an ampule containing a fluid to be injected, said ampule being received in said body in communication with said orifice, a first piston closing that end of said ampule remote from said orifice and movable toward said orifice to eject such Huid through said orifice, a second piston reciprocably received in said body and bearing axially on said first piston, a flexible tube having one end connected to the other end of said body, an elongated chamber connected to the other end of said tube, a third piston reciprocably mounted in said chamber, a column of liquid in said flexible tube providing a driving connection between said third piston and said second piston, and a pneumatic motor operatively connected to drive said third piston toward said tubular body, said pneumatic motor comprising a cylinder, a fourth piston reciprocably mounted in said cylinder, operatively connected to said third piston and having anetfective diameter significantly exceeding that of said lirst piston, a fifth piston reciprocably mounted in said cylinder and yieldably separated from said fourth piston in a direction remote from said third piston, said motor being formed to provide open communication between opposite sides of said fourth piston except when said fifth piston substantially engages said fourth piston, and said cylinder being provided with an inlet port at a point more remote from said third piston than is said fifth piston and with an outlet port at a point between said fourth piston and said third piston.
2. The system of claim 1 in which said fourth piston is axially ported to provide such open communication.
3. The system of claim 1 including a source of pneumatic liuid under pressure, conduit means connecting said source with said inlet port, and valve means disposed in said conduit means and controlling communication between said source and said inlet port.
4. The system of claim 1 in which said cylinder is provided with a bleed port normally located between said fourth piston and `said fifth piston, said bleed port providing communication between the atmosphere and the interior of said cylinder only when said fourth and fifth pistons have been advanced.
5. The system of claim 4 including adjustable Valve means associated with said bleed port to control the effective flow capacity of said vbleed port.
References Cited UNITED STATES PATENTS Re. 19,219 6/1934 Smith 128-218-1 2,547,099 4/1951 Smoot 128--173 2,688,325 9/1954 Lockhart 128-218 2,604,757 7/1952 Wulleman 60-54.5 2,669,230 2/1954 Smoot 128-173 2,904,043 9/1959 Friedman 12S-218.1 3,189,029 6/1965 Stephens 128-173 3,059,433 10/1962 Hirsch 60-54.5
RICHARD A. GAUDET, Primary Examiner.
KYLE L. HOWELL, Assistant Examiner.
U.S. Cl. X.R. 12S-218; 60-54.5
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2547099 *||Mar 11, 1948||Apr 3, 1951||Becton Dickinson Co||Injection device and ampoule|
|US2604757 *||Oct 8, 1949||Jul 29, 1952||Paul Duclos Ets||Hydraulic compensating and balancing device for reciprocal hydraulic remote-control circuits|
|US2669230 *||Jul 30, 1947||Feb 16, 1954||Becton Dickinson Co||Injection apparatus|
|US2688325 *||Sep 12, 1952||Sep 7, 1954||Compule Corp||Piston plug withdrawal limiting means for hypodermic syringe devices and the like|
|US2904043 *||Feb 10, 1954||Sep 15, 1959||Friedman Benjamin||Hypodermic syringes|
|US3059433 *||Feb 14, 1961||Oct 23, 1962||Hirsch George||Pressure and force multiplying devices|
|US3189029 *||Jul 27, 1961||Jun 15, 1965||Amalgamated Dental Co Ltd||Hypodermic injection apparatus|
|USRE19219 *||Jul 16, 1927||Jun 19, 1934||Ampule|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US3515130 *||Sep 18, 1967||Jun 2, 1970||Yuryo Kikakuhin Kenkyusho Kk||Jet-injection hypodermic device|
|US3742948 *||Aug 10, 1970||Jul 3, 1973||Philips Corp||Hypodermic syringe with radially movable blocking elements|
|US4007739 *||Jul 18, 1975||Feb 15, 1977||Dan Bron||Fluid-operated hypodermic syringe|
|US4145959 *||Feb 23, 1977||Mar 27, 1979||Teledyne Mccormick Selph, An Operating Division Of Teledyne Industries, Inc.||Constant speed actuator|
|US4177810 *||Feb 24, 1978||Dec 11, 1979||Damon Corporation||Pneumatic injection apparatus|
|US4280326 *||Nov 13, 1979||Jul 28, 1981||Health And Safety Executive||Generators of impulses|
|US4403609 *||Feb 24, 1981||Sep 13, 1983||Cohen Edgar C||Vacuum-compression injector|
|US4421508 *||Jul 8, 1981||Dec 20, 1983||Cohen Edgar C||Vacuum-compression injector|
|US5024656 *||Aug 30, 1988||Jun 18, 1991||Injet Medical Products, Inc.||Gas-pressure-regulated needleless injection system|
|US5116313 *||Aug 31, 1990||May 26, 1992||Her Majesty The Queen In Right Of Canada, As Represented By The National Research Council||Variable intensity remote controlled needleless injectors|
|US5399163 *||Jul 23, 1993||Mar 21, 1995||Bioject Inc.||Needleless hypodermic injection methods and device|
|US5520639 *||Mar 21, 1995||May 28, 1996||Bioject, Inc.||Needleless hypodermic injection methods and device|
|US5599302 *||Jan 9, 1995||Feb 4, 1997||Medi-Ject Corporation||Medical injection system and method, gas spring thereof and launching device using gas spring|
|US5643211 *||Feb 29, 1996||Jul 1, 1997||Medi-Ject Corporation||Nozzle assembly having a frangible plunger|
|US5697917 *||Feb 29, 1996||Dec 16, 1997||Medi-Ject Corporation||Nozzle assembly with adjustable plunger travel gap|
|US5722950 *||Jun 7, 1995||Mar 3, 1998||Atrix Laboratories, Inc.||Method for remote delivery of an aerosolized liquid|
|US5722953 *||Feb 29, 1996||Mar 3, 1998||Medi-Ject Corporation||Nozzle assembly for injection device|
|US5792469 *||Jun 7, 1995||Aug 11, 1998||Atrix Laboratories, Inc.||Biodegradable in situ forming film dressing|
|US5800388 *||Feb 29, 1996||Sep 1, 1998||Medi-Ject Corporation||Plunger/ram assembly adapted for a fluid injector|
|US5846233 *||Jan 9, 1997||Dec 8, 1998||Medi-Ject Corporation||Coupling device for medical injection system|
|US5865795 *||Feb 29, 1996||Feb 2, 1999||Medi-Ject Corporation||Safety mechanism for injection devices|
|US5875976 *||Dec 24, 1996||Mar 2, 1999||Medi-Ject Corporation||Locking mechanism for nozzle assembly|
|US5891085 *||Jan 9, 1997||Apr 6, 1999||Medi-Ject Corporation||Nozzle assembly with lost motion connection for medical injector assembly|
|US5919159 *||Jan 9, 1997||Jul 6, 1999||Medi-Ject Corporation||Medical injection system and method, gas spring thereof and launching device using gas spring|
|US5921967 *||Dec 24, 1996||Jul 13, 1999||Medi-Ject Corporation||Plunger for nozzle assembly|
|US5993412 *||May 19, 1997||Nov 30, 1999||Bioject, Inc.||Injection apparatus|
|US6641553 *||Jun 2, 2000||Nov 4, 2003||Boston Scientific Corporation||Devices and methods for delivering a drug|
|US6647953||Aug 30, 2001||Nov 18, 2003||Caterpillar Inc||Hydraulic system volume reducer|
|US6942638 *||May 30, 2002||Sep 13, 2005||Kerry Quinn||Needleless injector and ampule system|
|US7147633||Mar 14, 2002||Dec 12, 2006||Boston Scientific Scimed, Inc.||Method and apparatus for treatment of atrial fibrillation|
|US7618393||Nov 13, 2006||Nov 17, 2009||Pharmajet, Inc.||Needle-less injector and method of fluid delivery|
|US7699802||May 3, 2005||Apr 20, 2010||Pharmajet, Inc.||Needle-less injector|
|US8187251||Oct 31, 2006||May 29, 2012||Boston Scientific Scimed, Inc.||Methods of treating cardiac arrhythmia|
|US8496601||Apr 16, 2007||Jul 30, 2013||Sanofi-Aventis Deutschland Gmbh||Methods and apparatus for lancet actuation|
|US8529500||Jun 16, 2011||Sep 10, 2013||Pharmajet, Inc.||Needle-less injector and method of fluid delivery|
|US8556829||Jan 27, 2009||Oct 15, 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8562545||Dec 16, 2008||Oct 22, 2013||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8574168||Mar 26, 2007||Nov 5, 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for a multi-use body fluid sampling device with analyte sensing|
|US8574895||Dec 30, 2003||Nov 5, 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus using optical techniques to measure analyte levels|
|US8579831||Oct 6, 2006||Nov 12, 2013||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8622930 *||Jul 18, 2011||Jan 7, 2014||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8636673||Dec 1, 2008||Jan 28, 2014||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8641643||Apr 27, 2006||Feb 4, 2014||Sanofi-Aventis Deutschland Gmbh||Sampling module device and method|
|US8641644||Apr 23, 2008||Feb 4, 2014||Sanofi-Aventis Deutschland Gmbh||Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means|
|US8652831||Mar 26, 2008||Feb 18, 2014||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for analyte measurement test time|
|US8668656||Dec 31, 2004||Mar 11, 2014||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for improving fluidic flow and sample capture|
|US8679033||Jun 16, 2011||Mar 25, 2014||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8690796||Sep 29, 2006||Apr 8, 2014||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US8702624||Jan 29, 2010||Apr 22, 2014||Sanofi-Aventis Deutschland Gmbh||Analyte measurement device with a single shot actuator|
|US8721671||Jul 6, 2005||May 13, 2014||Sanofi-Aventis Deutschland Gmbh||Electric lancet actuator|
|US8784335||Jul 25, 2008||Jul 22, 2014||Sanofi-Aventis Deutschland Gmbh||Body fluid sampling device with a capacitive sensor|
|US8828203||May 20, 2005||Sep 9, 2014||Sanofi-Aventis Deutschland Gmbh||Printable hydrogels for biosensors|
|US8845549||Dec 2, 2008||Sep 30, 2014||Sanofi-Aventis Deutschland Gmbh||Method for penetrating tissue|
|US8845550 *||Dec 3, 2012||Sep 30, 2014||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US8905945||Mar 29, 2012||Dec 9, 2014||Dominique M. Freeman||Method and apparatus for penetrating tissue|
|US8945910||Jun 19, 2012||Feb 3, 2015||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for an improved sample capture device|
|US8965476||Apr 18, 2011||Feb 24, 2015||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US9034639||Jun 26, 2012||May 19, 2015||Sanofi-Aventis Deutschland Gmbh||Method and apparatus using optical techniques to measure analyte levels|
|US9072842||Jul 31, 2013||Jul 7, 2015||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US9089294||Jan 16, 2014||Jul 28, 2015||Sanofi-Aventis Deutschland Gmbh||Analyte measurement device with a single shot actuator|
|US9089678||May 21, 2012||Jul 28, 2015||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US9144401||Dec 12, 2005||Sep 29, 2015||Sanofi-Aventis Deutschland Gmbh||Low pain penetrating member|
|US9186468||Jan 14, 2014||Nov 17, 2015||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for penetrating tissue|
|US9226699||Nov 9, 2010||Jan 5, 2016||Sanofi-Aventis Deutschland Gmbh||Body fluid sampling module with a continuous compression tissue interface surface|
|US9248267||Jul 18, 2013||Feb 2, 2016||Sanofi-Aventis Deustchland Gmbh||Tissue penetration device|
|US9261476||Apr 1, 2014||Feb 16, 2016||Sanofi Sa||Printable hydrogel for biosensors|
|US9314194||Jan 11, 2007||Apr 19, 2016||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US9333300||Sep 5, 2013||May 10, 2016||Pharmajet, Inc.||Needle-less injector and method of fluid delivery|
|US9339612||Dec 16, 2008||May 17, 2016||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US9351680||Oct 14, 2004||May 31, 2016||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for a variable user interface|
|US9375169||Jan 29, 2010||Jun 28, 2016||Sanofi-Aventis Deutschland Gmbh||Cam drive for managing disposable penetrating member actions with a single motor and motor and control system|
|US9408972||Aug 2, 2011||Aug 9, 2016||Pharmajet, Inc.||Needle-free injection device|
|US9427532 *||Sep 29, 2014||Aug 30, 2016||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US9433735||Dec 12, 2012||Sep 6, 2016||Pharmajet Inc.||Needle-free intradermal injection device|
|US9498160||Sep 29, 2014||Nov 22, 2016||Sanofi-Aventis Deutschland Gmbh||Method for penetrating tissue|
|US9560993||Dec 20, 2013||Feb 7, 2017||Sanofi-Aventis Deutschland Gmbh||Blood testing apparatus having a rotatable cartridge with multiple lancing elements and testing means|
|US9561000||Dec 10, 2013||Feb 7, 2017||Sanofi-Aventis Deutschland Gmbh||Method and apparatus for improving fluidic flow and sample capture|
|US20020183738 *||Mar 14, 2002||Dec 5, 2002||Chee U. Hiram||Method and apparatus for treatment of atrial fibrillation|
|US20040030320 *||Aug 6, 2003||Feb 12, 2004||Boston Scientific Corporation||Devices and methods for delivering a drug|
|US20050256534 *||Jul 6, 2005||Nov 17, 2005||Don Alden||Electric lancet actuator|
|US20060161194 *||Dec 12, 2005||Jul 20, 2006||Freeman Dominique M||Low pain penetrating member|
|US20060195047 *||Apr 27, 2006||Aug 31, 2006||Freeman Dominique M||Sampling module device and method|
|US20060204399 *||Dec 30, 2003||Sep 14, 2006||Freeman Dominique M||Method and apparatus using optical techniques to measure analyte levels|
|US20070027428 *||Jun 15, 2006||Feb 1, 2007||Pharmajet, Inc.||Vial system and method for needle-less injector|
|US20070055230 *||Oct 31, 2006||Mar 8, 2007||Scimed Life Systems, Inc||Methods of treating cardiac arrhythmia|
|US20070073188 *||Sep 29, 2006||Mar 29, 2007||Freeman Dominique M||Method and apparatus for penetrating tissue|
|US20070118094 *||Nov 13, 2006||May 24, 2007||John Bingham||Needle-less injector and method of fluid delivery|
|US20070123802 *||Sep 25, 2006||May 31, 2007||Freeman Dominique M||Methods and apparatus for an analyte detecting device|
|US20070173741 *||Jan 11, 2007||Jul 26, 2007||Ajay Deshmukh||Tissue penetration device|
|US20070191762 *||Jul 21, 2005||Aug 16, 2007||Kerry Quinn||Needleless injector and ampule system|
|US20070219463 *||Apr 16, 2007||Sep 20, 2007||Barry Briggs||Methods and apparatus for lancet actuation|
|US20070219574 *||Mar 26, 2007||Sep 20, 2007||Dominique Freeman||Method and apparatus for a multi-use body fluid sampling device with analyte sensing|
|US20080021491 *||Jul 9, 2007||Jan 24, 2008||Freeman Dominique M||Method and apparatus for penetrating tissue|
|US20080027385 *||Oct 6, 2006||Jan 31, 2008||Freeman Dominique M||Method and apparatus for penetrating tissue|
|US20080194987 *||Oct 14, 2004||Aug 14, 2008||Pelikan Technologies, Inc.||Method and Apparatus For a Variable User Interface|
|US20080210574 *||Mar 26, 2008||Sep 4, 2008||Dirk Boecker||Method and apparatus for analyte measurement test time|
|US20080281261 *||May 3, 2005||Nov 13, 2008||Genesis Medical Technologies, Inc.||Needle-less injector|
|US20090005664 *||Apr 23, 2008||Jan 1, 2009||Dominique Freeman||Blood Testing Apparatus Having a Rotatable Cartridge with Multiple Lancing Elements and Testing Means|
|US20090024009 *||Jul 25, 2008||Jan 22, 2009||Dominique Freeman||Body fluid sampling device with a capacitive sensor|
|US20090069716 *||Oct 1, 2008||Mar 12, 2009||Dominique Freeman||Method and apparatus for a fluid sampling device|
|US20090112123 *||Dec 2, 2008||Apr 30, 2009||Dominique Freeman||Method for penetrating tissue|
|US20090124932 *||Dec 16, 2008||May 14, 2009||Dominique Freeman||Method and apparatus for penetrating tissue|
|US20090131829 *||Dec 16, 2008||May 21, 2009||Dominique Freeman||Tissue penetration device|
|US20090131964 *||Dec 16, 2008||May 21, 2009||Dominique Freeman||Tissue penetration device|
|US20090137930 *||Dec 16, 2008||May 28, 2009||Dominique Freeman||Tissue penetration device|
|US20090138032 *||Dec 1, 2008||May 28, 2009||Dominique Freeman||Tissue penetration device|
|US20090192410 *||Jan 26, 2009||Jul 30, 2009||Dominique Freeman||Universal diagnostic system|
|US20090192411 *||Jan 27, 2009||Jul 30, 2009||Dominique Freeman||Method and apparatus for penetrating tissue|
|US20090196580 *||Oct 6, 2006||Aug 6, 2009||Freeman Dominique M||Method and apparatus for an analyte detecting device|
|US20090209883 *||Jan 15, 2009||Aug 20, 2009||Michael Higgins||Tissue penetrating apparatus|
|US20100166607 *||May 20, 2005||Jul 1, 2010||Norbert Bartetzko||Printable hydrogels for biosensors|
|US20100204612 *||Jan 29, 2010||Aug 12, 2010||In Sang Choi||Cam drive for managing disposable penetrating member actions with a single motor and motor and control system|
|US20100286560 *||Jun 3, 2005||Nov 11, 2010||Dominique Freeman||Method and apparatus for a fluid sampling device|
|US20100292611 *||Dec 31, 2004||Nov 18, 2010||Paul Lum||Method and apparatus for improving fluidic flow and sample capture|
|US20110034829 *||Sep 25, 2006||Feb 10, 2011||Freeman Dominique M||Methods and apparatus for an analyte detecting device|
|US20110077478 *||Nov 9, 2010||Mar 31, 2011||Dominique Freeman||Body fluid sampling module with a continuous compression tissue interface surface|
|US20120130343 *||Jul 18, 2011||May 24, 2012||Dominique Freeman||Tissue penetration device|
|US20130096533 *||Dec 3, 2012||Apr 18, 2013||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|US20150126962 *||Sep 29, 2014||May 7, 2015||Sanofi-Aventis Deutschland Gmbh||Tissue penetration device|
|DE10116778A1 *||Apr 4, 2001||Oct 17, 2002||Roesch Ag Medizintechnik||Injektionseinrichtung|
|WO1982002835A1 *||Feb 24, 1982||Sep 2, 1982||Edgar C Cohen||Vacuum-compression injector|
|WO2002081009A2 *||Apr 4, 2002||Oct 17, 2002||Rösch Ag Medizintechnik||Injection device|
|WO2002081009A3 *||Apr 4, 2002||Dec 12, 2002||Stefan Matucha||Injection device|
|U.S. Classification||604/70, 604/150, 60/593, 604/71|
|International Classification||A61M5/20, A61M5/30|
|Cooperative Classification||A61M5/2053, A61M5/30|