US20100111708A1 - Fluid ejection system, fluid ejection system drive method, and surgical apparatus - Google Patents

Fluid ejection system, fluid ejection system drive method, and surgical apparatus Download PDF

Info

Publication number
US20100111708A1
US20100111708A1 US12/606,470 US60647009A US2010111708A1 US 20100111708 A1 US20100111708 A1 US 20100111708A1 US 60647009 A US60647009 A US 60647009A US 2010111708 A1 US2010111708 A1 US 2010111708A1
Authority
US
United States
Prior art keywords
generation section
fluid
pressure
load
pulsation
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US12/606,470
Other languages
English (en)
Inventor
Takeshi Seto
Kazuo Kawasumi
Kunio Tabata
Shinichi Miyazaki
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Seiko Epson Corp
Original Assignee
Seiko Epson Corp
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Seiko Epson Corp filed Critical Seiko Epson Corp
Assigned to SEIKO EPSON CORPORATION reassignment SEIKO EPSON CORPORATION ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: KAWASUMI, KAZUO, MIYAZAKI, SHINICHI, SETO, TAKESHI, TABATA, KUNIO
Publication of US20100111708A1 publication Critical patent/US20100111708A1/en
Abandoned legal-status Critical Current

Links

Images

Classifications

    • F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04—POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04B—POSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B43/00—Machines, pumps, or pumping installations having flexible working members
    • F04B43/02—Machines, pumps, or pumping installations having flexible working members having plate-like flexible members, e.g. diaphragms
    • F04B43/04—Pumps having electric drive
    • F04B43/043—Micropumps
    • F04B43/046—Micropumps with piezoelectric drive
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/32—Surgical cutting instruments
    • A61B17/3203—Fluid jet cutting instruments

Definitions

  • the present invention relates to a fluid ejection system including a fluid ejection apparatus and a control apparatus which carries out a control of the fluid ejection apparatus, a method of driving the fluid ejection system, and a surgical apparatus using the fluid ejection system and its drive method.
  • An advantage of some aspect of the invention is to solve at least a part of the problem described above and the invention can be realized as the following aspects or application examples.
  • a fluid ejection system includes a pulsation generation section which, including a fluid chamber, a diaphragm which changes a volume of the fluid chamber, and a piezoelectric element which drives the diaphragm, pulsatively ejects a fluid from a nozzle; and a control apparatus including a pressure generation section which supplies the fluid to the fluid chamber at a predetermined pressure, a drive waveform generation section which inputs a drive waveform into the piezoelectric element, and a load detection section which detects a load of the pressure generation section.
  • a fluid discharge pressure amplitude of the pulsation generation section or a fluid supply pressure of the pressure generation section is made higher than at a normal drive time.
  • the normal drive time means a drive status when actually using the fluid ejection system.
  • the load of the pressure generation section falls within an approximately constant range.
  • the load of the pressure generation section increases.
  • the drive waveform is configured of a pulsation portion and a quiescent portion, and that, in the event that the load detection section has detected a load abnormality of the pressure generation section, the amplitude of the pulsation portion is made larger than the amplitude at the normal drive time.
  • the drive waveform is configured of the pulsation portion formed of a whole number of sequential waveforms, and the quiescent portion in which no waveform is output, by appropriately selecting an amplitude (a potential) and frequency of the pulsation portion, an ejection of a fluid group forms a pulsation necessary for an excision capability. Also, a quiescent time enables a control of a flow rate.
  • the drive waveform input in the event that the load detection section has detected a load abnormality of the pressure generation section is configured of a continuous pulsation portion.
  • a frequency of the drive waveform input in the event that the load detection section has detected a load abnormality of the pressure generation section approximately matches a resonant frequency of a pressure wave propagated through a space from the fluid chamber to the nozzle.
  • the amplitude of the pulsation portion is made larger than the amplitude at the normal drive time, and the pressure at which the pressure generation section supplies the fluid to the fluid chamber is made higher than that at the normal drive time.
  • the amplitude of the pulsation portion When the amplitude of the pulsation portion is made larger, the amount of the volume contraction of the fluid chamber increases, as previously described. By this means, as well as the fluid discharge pressure becoming higher, the discharge amount increases. Therein, as the amount of fluid supplied to the fluid chamber is increased by increasing the pressure at which the fluid is supplied by the pressure generation section, it is possible to supply a sufficient amount of liquid to the pulsation generation section in response to an increase in the discharge amount.
  • a load of the pressure generation section is detected as a change in a drive speed of a fluid delivery device of the pressure generation section.
  • the pressure generation section being, for example, a pump
  • a fluid delivery device such as a piston pump or a gear pump.
  • a change in the drive speed of the fluid delivery device can be easily and accurately measured by a linear encoder in the case of the piston pump, or a rotary encoder in the case of the gear pump.
  • the load detection section in the event that the drive speed has become equal to or less than a prescribed value, determines that there is a load abnormality of the pressure generation section.
  • the load detection section is a pressure sensor provided inside the pressure generation section.
  • the fluid ejection system it is preferable that it further includes an alarm which, in the event that the load detection section has detected a load abnormality of the pressure generation section, informs of the abnormality.
  • the fluid ejection system it is preferable that it further includes an operating member which, after the load detection section has detected a load abnormality of the pressure generation section, and the drive of the pulsation generation section and pressure generation section has been stopped, switches in such a way as to make the fluid discharge pressure of the pulsation generation section or the fluid supply pressure of the pressure generation section higher than at the normal drive time.
  • the operating member is provided on the pulsation generation section.
  • the pulsation generation section is gripped when operated. Consequently, by providing the operating member on the pulsation generation section, it is possible for the surgeon him or herself to carry out the switching operation at hand, and remove a clogging.
  • the drive waveform is configured of a combination of a midpoint potential, at which the piezoelectric element is charged to the extent that the fluid is moved to a position in which it reaches the leading extremity of the nozzle, and a potential at which the piezoelectric element is discharged.
  • a fluid ejection system drive method is a method of driving a fluid ejection system including: a pulsation generation section which, including a fluid chamber, a diaphragm which changes a volume of the fluid chamber, and a piezoelectric element which drives the diaphragm, pulsatively ejects a fluid from a nozzle; and a control apparatus including a pressure generation section which supplies the fluid to the fluid chamber at a predetermined pressure, a drive waveform generation section which inputs a drive waveform into the piezoelectric element, and a load detection section which detects a load of the pressure generation section.
  • the method includes a step of, during a normal drive of the fluid ejection system, detecting a load of the pressure generation section, which supplies the fluid to the pulsation generation section at the predetermined pressure, by means of the load detection section; a step of outputting an alarm in the event that the load of the pressure generation section has become equal to or more than a prescribed value; a step of stopping the drive of the pulsation generation section and pressure generation section; a cleaning step in which a fluid discharge pressure of the pulsation generation section or a fluid supply pressure of the pressure generation section is made higher than at a normal drive time; and a step of restoring the normal drive after finishing the cleaning step.
  • a surgical apparatus includes the fluid ejection system described in the heretofore mentioned application example, and is driven by the previously described fluid ejection system drive method.
  • FIG. 1 is an illustration showing an outline configuration of a fluid ejection system according to Embodiment 1.
  • FIG. 2 is a sectional view showing a main configuration of a pulsation generation section according to Embodiment 1, taken along a direction of a channel of a liquid.
  • FIG. 3 is a configuration diagram showing a main system configuration of the fluid ejection system according to Embodiment 1.
  • FIG. 4 is an illustration illustrating one example of a drive waveform according to Embodiment 1.
  • FIG. 5 is an illustration showing a method of driving the fluid ejection system according to Embodiment 1.
  • FIG. 6 is an illustration showing a drive waveform input during an idle period according to Embodiment 5.
  • FIGS. 7A to 7C are fragmentary sectional views schematically representing a behavior of a pulsation generation section according to Embodiment 5.
  • FIGS. 1 to 5 show a fluid ejection system according to Embodiment 1
  • FIGS. 6 and 7A to 7 C show Embodiment 5.
  • the fluid ejection system can be variously employed for a drawing using ink or the like, a washing of a miniature object and structure, a cutting off or cutting out of an object, an electronic instrument cooling device, a surgical knife, and the like, but in the embodiments to be described hereafter, a description will be given exemplifying with a surgical apparatus suitable in incising or excising a body tissue. Consequently, a fluid used in the embodiments being a liquid such as water, saline, or a chemical, the fluid may be expressed as the liquid.
  • FIG. 1 is an illustration showing an outline configuration of the fluid ejection system according to Embodiment 1.
  • the fluid ejection system 1 is configured of a control apparatus 100 , which includes a liquid storage container storing a liquid, a fluid delivery device of a pump acting as a pressure generation section, and a drive waveform generation section (which are not shown), a fluid ejection apparatus 10 which pulsatively ejects the liquid supplied from the fluid delivery device, and a fluid supply tube 25 (hereafter expressed simply as a tube 25 ) which brings the fluid ejection apparatus 10 into communication with the pump.
  • a control apparatus 100 which includes a liquid storage container storing a liquid, a fluid delivery device of a pump acting as a pressure generation section, and a drive waveform generation section (which are not shown), a fluid ejection apparatus 10 which pulsatively ejects the liquid supplied from the fluid delivery device, and a fluid supply tube 25 (hereafter expressed simply as a tube 25 ) which brings the fluid ejection
  • control apparatus 100 and fluid ejection apparatus 10 are electrically connected by a drive signal cable 15 and operation switching signal cable 16 .
  • the liquid storage container, the pump, the drive waveform generation section, and a system control section, which controls the whole of the system, are included inside the control apparatus 100 , and a display section 161 , which displays a drive condition and drive status, an adjustment member 160 , which sets an optimum drive waveform, and an alarm 144 , are provided on the external side.
  • the fluid ejection apparatus 10 includes a pulsation generation section 30 , which causes the supplied liquid to pulsate at a high pressure and high frequency, and a connection channel pipe 90 , which is connected to the pulsation generation section 30 .
  • a nozzle 95 including a fluid ejection opening 97 which is formed by reducing the sectional area of the channel, is inserted in the leading extremity of the connection channel pipe 90 .
  • the liquid stored in the liquid storage container included in the control apparatus 100 is supplied by the pump at a certain pressure to the pulsation generation section 30 via the tube 25 .
  • the pulsation generation section 30 being provided with a fluid chamber 120 (refer to FIG. 2 ) and the fluid chamber 120 's volume changing unit, by driving the volume changing unit, generates a pulsation, and ejects the liquid in a pulse form from the fluid ejection opening 97 .
  • a detailed description of the pulsation generation section 30 will be given hereafter, referring to FIGS. 2 to 4 .
  • a discharge pressure of the pump at a normal drive time is set to approximately three atmospheres (0.3 MPa) or less.
  • a main portion which a surgeon grips is the pulsation generation section 30 . Consequently, it is preferable that the tube 25 connected to the pulsation generation section 30 is as flexible as possible. For that purpose, it is preferable that it is made a flexible and thin tube, and that the pressure is made low within a range in which it is possible to send the liquid to the pulsation generation section 30 .
  • FIG. 2 is a sectional view showing a main configuration of the pulsation generation section according to Embodiment 1, taken along a liquid channel direction.
  • the fluid ejection apparatus 10 is configured of the pulsation generation section 30 , the connection channel pipe 90 connected to the pulsation generation section 30 , and the nozzle 95 inserted in the connection channel pipe 90 .
  • the pulsation generation section 30 includes a ring shaped spacer 60 closely clamped between the mutually opposed surfaces of a first machine casing 80 and second machine casing 50 , and a diaphragm 70 which, acting as the volume changing unit, is made of a disk shaped sheet metal, and the fluid chamber 120 is configured by a wall surface 80 a of the first machine casing 80 , the diaphragm 70 , and the inner peripheral wall surface of the spacer 60 .
  • a tube connection pipe 81 is protruded from the outer side surface of the first machine casing 80 , and an inflow connection channel 84 is opened in the tube connection pipe 81 .
  • the inflow connection channel 84 is brought into communication with an inlet channel 83 communicating with the flow chamber 120 .
  • the tube 25 is pressed into the tube connection pipe 81 .
  • the tube 25 is connected to the pump provided inside the control apparatus 100 (refer to FIG. 1 ), and the liquid is supplied into the flow chamber 120 via the inflow connection channel 84 and inlet channel 83 .
  • an outlet channel 88 is opened, and furthermore, an outlet connection channel 89 communicating with the outlet channel 88 is opened, in an approximate center of the wall surface 80 a so as to be approximately perpendicular to the wall surface 80 a of the first machine casing 80 .
  • connection channel pipe insertion portion 82 is protruded in a direction opposite to the fluid chamber 120 , and the outlet connection channel 89 communicating with the outlet channel 88 is provided, in the first machine casing 80 .
  • the connection channel pipe 90 is pressed into and fixed in the connection channel pipe insertion portion 82 .
  • connection channel pipe 90 being pressed into and fixed in the connection channel pipe insertion portion 82 , it is also acceptable to adopt a removable structure in which threaded portions are formed in the connection channel pipe 90 and connection channel pipe insertion portion 82 , and the connection channel pipe 90 is screwed into and fixed in the connection channel pipe insertion portion 82 .
  • connection channel 92 communicating with the outlet connection channel 89 is opened in the connection channel pipe 90 , and the nozzle 95 is pressed into a leading extremity of the connection channel pipe 90 opposite the outlet channel 88 .
  • the nozzle 95 includes a nozzle channel 96 communicating with the connection channel 92 , and the fluid ejection opening 97 .
  • the outlet connection channel 89 , connection channel 92 , and nozzle channel 96 have approximately the same sectional area, and this sectional area is larger than the sectional area of the outlet channel 88 . Also, the sectional area of the fluid ejection opening 97 is reduced in comparison with the sectional area of the connection channel 92 , and furthermore, reduced in comparison with that of the outlet channel 88 .
  • the sectional area represents the sectional area of the channel when sectioned perpendicular to a liquid flow direction.
  • the diameter of the outlet channel 88 is set to 0.3 mm, the diameter of the connection channel 92 to 1.0 mm, and the diameter of the fluid ejection opening 97 within a range of 0.1 to 0.2 mm. Also, the channel length from the fluid chamber 120 to the fluid ejection opening 97 is appropriately set within a range of 100 to 200 mm.
  • the second machine casing 50 being a cylindrical member, has opened therein a cylindrical hole 52 passing through the second machine casing 50 .
  • One of the openings of the hole 52 is sealed with a lower plate 102 .
  • a piezoelectric element 40 acting as a drive source is disposed inside the hole 52 .
  • the piezoelectric element 40 being a stacked piezoelectric element, configures a columnar actuator.
  • One extremity of the piezoelectric element 40 is closely fixed to the diaphragm 70 across an upper plate 101 , and the other extremity to the inner surface of the lower plate 102 .
  • Drive electrodes (not shown) are provided one on each of the opposed side surfaces of the piezoelectric element 40 , and the drive signal cable 15 formed of connection leads 15 a and 15 b coated in insulation is connected to the drive electrodes.
  • the drive signal cable 15 being extended outward through a through hole 53 opened in a side surface of the second machine casing 50 , is connected to a drive waveform generation section 151 (refer to FIG. 3 ) included in the control apparatus 100 .
  • the through hole 53 is sealed with a seal member 103 in a condition in which the drive signal cable 15 is put through the through hole 53 .
  • the pulsation generation section 30 having its periphery hermetically sealed, is covered with a contour member which is attachable to and detachable from the pulsation generation section 30 .
  • the contour member is configured of an upper casing 35 and lower casing 36 as a case member.
  • the upper casing 35 and lower casing 36 hold the pulsation generation section 30 in such a way as to sandwich the connection channel pipe insertion portion 82 of the first machine casing 80 and the cylindrical portion of the second machine casing 50 .
  • the upper casing 35 and lower casing 36 are fixed by unshown fixing screws. Consequently, the upper casing 35 and lower casing 36 are of a structure such that they are attachable to and detachable from the pulsation generation section 30 .
  • a packing acting as a seal member, being provided between the mutually opposed end faces of the upper casing 35 and lower casing 36 , hermetically seals the pulsation generation section 30 .
  • An operating member 130 is provided on the pulsation generation section 30 .
  • the operating member 130 being a switch, it is possible to select a push button type, a slide type, a rotary type, or the like, but the push button type switch is more preferable from the aspect of a space saving and a simple operation.
  • the operating member 130 being disposed in such a way that everything other than an operation section is embedded in the lower casing 36 , is connected to the control apparatus 100 by the operation switching signal cable 16 (refer to FIG. 1 ).
  • FIG. 3 is a configuration diagram showing a main system configuration of the fluid ejection system according to this embodiment.
  • the fluid ejection apparatus 10 is configured of the fluid chamber 120 , the diaphragm 70 acting as the volume changing unit which changes the volume of the fluid chamber 120 , the piezoelectric element 40 which drives the diaphragm 70 , and the operating member 130 .
  • the control apparatus 100 includes the liquid storage container 141 (hereafter expressed simply as the container 141 ), and a load detection section 142 which, including the pump 140 communicating with the container 141 , and a pump drive control section 143 which controls a drive of the pump 140 , detects a load fluctuation of the pump 140 .
  • the pump 140 it is possible to employ a liquid delivery device such as a piston pump or a gear pump, and it is brought into communication with the fluid chamber 120 by the tube 25 .
  • the load detection section 142 includes a linear encoder in the case of the piston pump, and a rotary encoder in the case of the gear pump, and detects a load fluctuation of the pump 140 as a change in piston drive speed or gear rotation speed.
  • the alarm 144 which, in the event that a clogging has occurred in the pulsation generation section 30 , and the load (drive speed) of the pump 140 has become equal to or more than a prescribed value, determines that the load is abnormal, and gives an alarm.
  • the alarm 144 can employ a sound of a buzzer or the like, or a light alert.
  • control apparatus 100 includes an optimum drive parameter calculation section 152 which calculates a drive waveform corresponding to the hardness of an excised tissue, the adjustment member 160 which inputs the excised tissue hardness, and the drive waveform generation section 151 which, based on an optimum drive parameter, generates a drive waveform to be input into the piezoelectric element 40 .
  • the control apparatus 100 further includes the system control section 150 which governs the overall control of each system component, and the display section 161 .
  • the display section 161 displays a drive condition such as the excised tissue hardness, a drive status, and the like.
  • a rotary switch being suitable as the adjustment member 160 , by rotating a dial thereof, a drive condition such as the excised tissue hardness is selected, and input into the optimum drive parameter calculation section 152 .
  • An amplitude (a potential), cycle, waveform quantity (pulse quantity), quiescent time, and the like, of a pulsation portion compatible with the selected and input excised tissue hardness or the like, are calculated in the optimum drive parameter calculation section 152 , and input into the piezoelectric element 40 , via the drive signal cable 15 , as an optimum drive waveform in the drive waveform generation section 151 .
  • FIG. 4 illustrates one example of a drive waveform according to this embodiment.
  • the drive waveform in this illustration is configured of a pulsation portion configured of a whole number of sequential sinusoidal waveforms in which a piezoelectric element drive voltage starts with a phase ⁇ /2, and a quiescent portion (expressed as a quiescent time I).
  • the drive waveform expressed by the solid line represents the normal drive time
  • the waveform of the pulsation portion is expressed by an amplitude A 1 , a cycle T, and a number n of sequential sine waves.
  • the number of sine waves is taken to be two.
  • the waveform of this pulsation portion being of a burst wave, it is possible, in the drive waveform generation section 151 , to generate it easily by specifying the heretofore mentioned parameter.
  • the drive waveform not being limited to that of the sine wave, it is also acceptable that it is of a combination of rectangular waves.
  • the liquid is constantly supplied to the inlet channel 83 at a certain fluid pressure by the pump 140 .
  • the piezoelectric element 40 carries out no operation, the liquid flows into the fluid chamber 120 due to a difference between a discharge pressure of the pump 140 and the whole fluid resistance value on the inlet channel side.
  • a pressure fluctuation (that is, a pressure wave) at this discharge time is propagated through the connection channel 92 of the connection channel pipe 90 , and the liquid is ejected in a pulse form from the fluid ejection opening 97 of the nozzle 95 (for both of which refer to FIG. 2 ) at the leading extremity.
  • the diameter of the fluid ejection opening 97 is reduced in comparison with the diameter of the outlet channel 88 , the liquid is ejected as higher-pressure and higher-speed pulse-like droplets.
  • the interior of the fluid chamber 120 attains a vacuum condition immediately after the pressure rise, due to an interaction between the decrease in the amount of liquid inflow from the inlet channel 83 and the increase in the liquid outflow from the outlet channel 88 .
  • a flow of the liquid in the inlet channel 83 moving toward the interior of the fluid chamber 120 at the same speed as that before the piezoelectric element 40 operates is restored, after a certain time has elapsed, due to both the pressure of the pump and the vacuum condition inside the fluid chamber 120 .
  • a pulsation intensity that is, a fluid discharge pressure amplitude is large
  • the fluid discharge pressure amplitude can be realized by increasing an amplitude A of a piezoelectric element drive voltage. Meanwhile, however, an amount of fluid ejected per unit time is also increased at the same time. As a result, an excision depth per unit time is also increased at the same time.
  • the fluid ejection section drive voltage amplitude A which is one of control parameters, changes, and at the same time, an adjustment is made by the optimum drive parameter calculation section 152 in such a way that the quiescent time I, which is another control parameter, changes, and the excision depth does not change.
  • optimum drive parameter table in place of the optimum drive parameter calculation section 152 .
  • the excised tissue hardness is selected by the adjustment member 160 , and an optimum drive parameter is selected from the optimum drive parameter table, generating a drive waveform. It is more preferable that information on the optimum drive parameter selected is displayed in the display section 161 .
  • the optimum drive parameter table is a table in which are combined control parameters such as a surgery type, the diameter of the fluid ejection opening 97 , an excised tissue hardness, and an excision depth.
  • the diameter of the fluid ejection opening 97 is extremely small at around 0.1 to 0.2 mm, and the outlet channel 88 communicating with the nozzle from the fluid chamber 120 is also extremely small at around 0.3 mm, it is also conceivable that a clogging occurs in a channel from the fluid chamber 120 to the fluid ejection opening 97 . Consequently, a removal of these cloggings, that is, a cleaning, is needed.
  • FIG. 5 is an illustration showing the drive method relating to the cleaning of this embodiment. A description will be given, referring to FIGS. 2 to 4 too, in accordance with the process shown in FIG. 5 .
  • the fluid ejection system 1 is started, starting a normal drive (ST 10 ). While the fluid ejection system is being driven, a load fluctuation of the pump 140 is being detected by the load detection section 142 (ST 20 ). As previously described, a load fluctuation is detected as a change in the drive speed of the fluid delivery device of the pump 140 .
  • the load of the pump 140 falls within an approximately constant range, and the fluid delivery device continues to be driven within a certain drive speed range.
  • the fluid ejection system 1 continues to be driven as it is (ST 30 ) and, when the surgery is finished, the fluid ejection system is stopped (ST 40 ).
  • a signal is input into the system control section 150 from the load detection section 142 , and an alarm is output using a sound, light, or the like by the alarm 144 (ST 50 ).
  • a drive stop command is output to the drive waveform generation section 151 and pump drive control section 143 from the system control section 150 , stopping the fluid ejection system 1 (ST 60 ).
  • a cleaning start operation after the pulsation generation section 30 has been moved away from a living body, is carried out by means of a switch input from the operating member 130 provided on the pulsation generation section 30 .
  • a cleaning start command from the operating member 130 is input into the system control section 150 via the operation switching signal cable 16 , and the pump 190 and pulsation generation section 30 are started based on the system control section 150 drive start command, starting the cleaning operation (ST 170 ).
  • the liquid discharge pressure amplitude of the pulsation generation section 30 is made higher than at the normal drive time.
  • the liquid discharge pressure amplitude of the pulsation generation section 30 can be made higher by making the amplitude of the pulsation portion of the drive waveform larger than at the normal drive time.
  • the drive waveform in that case is illustrated by the broken line in FIG. 4 .
  • an amplitude A 2 is made approximately twice as high as the amplitude A 1 at the normal drive time.
  • the surgeon when determining that the clogging has been removed, operates the operating member 130 again, stops the pulsation generation section 30 and pump 140 , and finishes the cleaning operation (ST 80 ).
  • the determination of the clogging removal is carried out by observing a discharge condition of the liquid from the liquid ejection opening 97 .
  • the operating member 130 is operated, and a start command from the system control section 150 is input, starting the fluid ejection system 1 (specifically, the pulsation generation section 30 and pump 140 ).
  • a drive waveform output at this time is the drive waveform at the normal drive time (refer to FIG. 4 ). Then, the process in and after ST 20 is repeated.
  • a setting is such that a detection reference value of the load detection section 192 is matched with the pump drive speed at a cleaning operation time.
  • a restart of the fluid ejection system is carried out by operating the operating member 130 . Consequently, it is preferable that the operating member 130 is a one-circuit two-contact type switch.
  • the liquid supply pressure of the pump 140 is made higher.
  • the liquid supply pressure of the pump 140 is made higher.
  • the amplitude (potential) thereof is changed with the cycle T and quiescent time I thereof remaining the same as those of the pulsation portion at the normal drive time, but it is also acceptable that the cycle T is changed, or the quiescent time I is changed.
  • the fluid ejection system of this embodiment by detecting that the load of the pump 140 has increased, it is determined that a clogging has occurred in the channel from the fluid chamber 120 to the fluid ejection opening 97 . Therein, it is possible to eliminate the clogging by making the fluid discharge pressure amplitude of the pulsation generation section 30 higher than at the normal drive time, and clean the channel from the fluid chamber 120 to the fluid ejection opening 97 .
  • the amplitude of the pulsation portion When the amplitude of the pulsation portion is made higher, the amount of the volume contraction of the fluid chamber 120 increases, as previously described. By this means, as well as the fluid discharge pressure amplitude becoming higher, the discharge amount increases. Therein, as the amount of fluid supplied to the fluid chamber 120 increases by increasing the fluid supply pressure applied by the pump 140 , it is possible to supply a sufficient amount of liquid to the pulsation generation section 30 in response to an increase in the discharge amount.
  • a change in load of the pump 140 is detected as a change in the drive speed of the fluid delivery device of the pump 140 .
  • the pressure inside this channel rises. Then, the load of the pump 140 increases, and the drive speed decreases. Consequently, it is possible to carry out a clogging determination by detecting a decrease in the drive speed.
  • the alarm 144 which informs of an abnormality in the event that the load detection section 142 has detected an increase in the load of the pump 140 which is equal to or more than the prescribed value.
  • the detection of a load abnormality of the pump 140 is done by a method which determines it to be abnormal when it is detected instantaneously, or by a method which determines it to be abnormal when it continues for, for example, several seconds.
  • the alarm 144 is disposed in the control apparatus 100 , but it is also acceptable that it is disposed in the pulsation generation section 30 .
  • the pulsation generation section 30 is made as light and small as possible. For this reason, it is more preferable to dispose it in the control apparatus 100 .
  • the alarm 144 is disposed independently in a position which is distant from the control apparatus 100 , the pulsation generation section 30 and easy to recognize.
  • the pulsation generation section 30 includes the operating member 130 . After a clogging has been detected, and the pulsation generation section has stopped, the surgeon consciously carries out a switching operation of the operating member 130 , causing a cleaning operation. By so doing, it not happening that a high pressure liquid ejection is unconsciously started, it is possible to increase the safety.
  • the drive waveform at the normal drive time of the fluid ejection system according to this embodiment is configured of a pulsation portion and quiescent portion, as expressed by the solid line in FIG. 4 .
  • the drive waveform input at the cleaning operation time in the event that the load detection section 142 has detected an increase in load (a load abnormality) of the pump 140 is configured of a continuous waveform. That is, it is configured of only a continuous pulsation portion without the quiescent time I.
  • the amplitude of the pulsation portion is larger than at the normal drive time, and the pulsation portion of the amplitude A 2 expressed in FIG. 4 forms a continuous drive waveform.
  • the amplitude of the pulsation portion is made larger than at the normal drive time, thereby increasing the fluid discharge pressure.
  • Embodiment 3 has a feature wherein the frequency of a drive waveform input in the event that the load detection section 142 has detected an increase in load (a load abnormality) of the pump 140 approximately matches the resonant frequency of a pressure wave propagated through a space from the fluid chamber 120 to the nozzle 95 .
  • the liquid converted into a pulsation flow by the pulsation generation section 30 by the pressure wave propagated from the fluid chamber 120 to the nozzle 95 , is ejected from the nozzle 95 as pulse-like droplets at a high speed.
  • one portion of the pressure wave is reflected at a nozzle position, and directed toward the fluid chamber 120 .
  • the pressure wave reciprocates in a portion, whose sectional area is extremely small, of a channel from the fluid chamber 120 to the nozzle 95 .
  • a distance from the fluid chamber 120 to the nozzle 95 is set to be 100 to 200 mm. Also, the propagation speed of the pressure wave from the fluid chamber 120 to the nozzle 95 is approximately 1500 m per second.
  • the distance from the fluid chamber 120 to the nozzle 95 is 150 mm, it is 300 mm there and back, and the resonant frequency of the pressure wave is 5 kHz. Consequently, the frequency of the drive waveform is taken to be 5 kHz.
  • Embodiment 4 has a feature wherein a pressure sensor is included inside the pump 140 .
  • the pressure inside the channel rises, causing an output load of the pump 140 .
  • the internal pressure of the pump 140 rises.
  • the pressure sensor is disposed in a fluid chamber (a pressure chamber) inside the pump 140 .
  • a difference between an internal pressure of the pump 140 at the normal drive time and at a clogging occurrence time is set in advance and, in the event that a rise in the pressure is equal to or more than a prescribed value, a cleaning operation is started.
  • the cleaning operation can be carried out in accordance with the process described in the illustration shown in FIG. 5 .
  • Embodiment 5 has a feature wherein a drive waveform is formed such that it is possible to prevent a clogging due to a drying or the like in the channel from the fluid chamber 120 to the fluid ejection opening 97 while temporarily halting the fluid ejection system halfway through a surgery.
  • FIG. 6 is an illustration showing a drive waveform input during an idle period according to this embodiment
  • FIGS. 7A to 7C are fragmentary sectional views schematically representing a behavior of the pulsation generation section in response to the drive waveform.
  • one cycle of the drive waveform is configured of a combination of, firstly, an area 1 in which a midpoint potential is held for a certain time, continuing, an area 2 in which the piezoelectric element 40 is discharged, and an area 3 in which the piezoelectric element 40 is charged with the midpoint potential after a certain time elapses.
  • FIG. 7A represents a condition in which the midpoint potential (indicated by a potential A 3 ) shown by 1 in FIG. 6 is applied to the piezoelectric element 40 .
  • the amount of charge of the piezoelectric element 40 is intermediate with respect to a full charge, and the amount of expansion is also intermediate with respect to a full charge amount. Consequently, the amount of the volume of the fluid chamber 120 contracted by the diaphragm 70 is also of an intermediate value.
  • the liquid rather than being discharged from the fluid ejection opening 97 of the nozzle 95 , remains to the extent that one portion thereof peeps out of the leading extremity.
  • the piezoelectric element 40 On the discharge potential (a potential ⁇ A 3 ) expressed by 2 in FIG. 6 being applied in this condition, the piezoelectric element 40 is discharged, attaining the condition represented in FIG. 7B . That is, a condition is attained in which the diaphragm 70 expands the volume of the fluid chamber 120 .
  • the pressure of the fluid chamber 120 decreases instantaneously, and the liquid in the nozzle 95 is retracted into the fluid chamber 120 by an amount by which the volume of the fluid chamber 120 has increased.
  • a potential A 1 higher than the midpoint potential is applied to the piezoelectric element 40 .
  • the piezoelectric element 40 expands by being fully charged, the volume of the fluid chamber 120 is contracted to the maximum by the diaphragm 70 , and the liquid is discharged as droplets 200 in the pulse form.
  • the pulsation generation section drive idle period (a surgery suspension period), by constantly repeating a movement of the liquid to the extent that the liquid is not discharged from the nozzle 95 , it is possible to suppress the clogging in the channel from the fluid ejection opening 97 to the fluid chamber 120 .
  • FIG. 6 illustrates the case in which the drive waveform is of a rectangular wave, but it is also acceptable that the drive waveform is of a combined sine wave.
  • the fluid ejection system 1 can be variously employed for a drawing using ink or the like, a washing of a miniature object and structure, a cutting off or cutting out of an object, a surgical knife, and the like, but is suitable as a surgical instrument with which a body tissue is incised or excised.

Landscapes

  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • Surgery (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Mechanical Engineering (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Reciprocating Pumps (AREA)
  • Surgical Instruments (AREA)
  • Control Of Positive-Displacement Pumps (AREA)
US12/606,470 2008-10-30 2009-10-27 Fluid ejection system, fluid ejection system drive method, and surgical apparatus Abandoned US20100111708A1 (en)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2008-279336 2008-10-30
JP2008279336A JP2010106748A (ja) 2008-10-30 2008-10-30 流体噴射システム、流体噴射システムの駆動方法、手術装置

Publications (1)

Publication Number Publication Date
US20100111708A1 true US20100111708A1 (en) 2010-05-06

Family

ID=42131611

Family Applications (1)

Application Number Title Priority Date Filing Date
US12/606,470 Abandoned US20100111708A1 (en) 2008-10-30 2009-10-27 Fluid ejection system, fluid ejection system drive method, and surgical apparatus

Country Status (2)

Country Link
US (1) US20100111708A1 (enExample)
JP (1) JP2010106748A (enExample)

Cited By (10)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20110208224A1 (en) * 2010-02-22 2011-08-25 Seiko Epson Corporation Liquid injection device
US20120163998A1 (en) * 2010-12-24 2012-06-28 Seiko Epson Corporation Fluid ejection device and medical device
US20130218184A1 (en) * 2007-08-10 2013-08-22 Seiko Epson Corporation Fluid injection device
EP2783644A1 (en) * 2013-03-28 2014-10-01 Seiko Epson Corporation Fluid ejection device and medical apparatus
US20150088176A1 (en) * 2013-09-20 2015-03-26 Seiko Epson Corporation Medical apparatus system and liquid supply device
US20160367278A1 (en) * 2014-12-24 2016-12-22 Seiko Epson Corporation Liquid ejection control device, liquid ejection system, and control method
US9610120B2 (en) 2013-10-09 2017-04-04 Olympus Corporation High-frequency treatment tool for endoscope
US10159996B2 (en) * 2014-10-20 2018-12-25 Akurate Dynamics LLC System for dispensing multiple component chemical sprays
US11014105B2 (en) 2016-10-15 2021-05-25 Akurate Dynamics, Llc Multi-segment heated hose having segment-specific heating means
US11826767B2 (en) 2020-03-16 2023-11-28 Seiko Epson Corporation Liquid ejection device

Families Citing this family (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP5546511B2 (ja) * 2010-09-13 2014-07-09 ボッシュ株式会社 還元剤噴射装置及びその制御方法
JP2012100799A (ja) * 2010-11-09 2012-05-31 Seiko Epson Corp 液体噴射システム及び液体噴射方法
JP2013027589A (ja) * 2011-07-29 2013-02-07 Seiko Epson Corp 流体噴射装置及び医療機器
JP5703742B2 (ja) * 2010-12-24 2015-04-22 セイコーエプソン株式会社 流体噴射装置、および医療機器
KR101294067B1 (ko) * 2011-08-30 2013-08-07 현대자동차주식회사 Ｓｃｒ 시스템의 우레아 분사 노즐의 막힘 방지 방법
JP5922533B2 (ja) * 2012-09-06 2016-05-24 富士フイルム株式会社 送気システム
KR102567682B1 (ko) * 2022-12-12 2023-08-18 농업회사법인 뉴건강나라 주식회사 스마트팜 근권부 건전성 관리를 위한 ai 분무식 재배 및 폐수 최소화 방법

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5205819A (en) * 1989-05-11 1993-04-27 Bespak Plc Pump apparatus for biomedical use
US20040099752A1 (en) * 2002-11-26 2004-05-27 Nordson Corporation Metered liquid dispensing system
US20050140718A1 (en) * 2003-12-25 2005-06-30 Seiko Epson Corporation Capping unit and control method for same, liquid droplet ejection apparatus and device manufacturing method
US20050211166A1 (en) * 2002-01-15 2005-09-29 Engel Harold J Pump
WO2008023300A1 (en) * 2006-08-21 2008-02-28 Koninklijke Philips Electronics N. V. Drug delivery device with piezoelectric actuator
US20080221523A1 (en) * 1998-10-29 2008-09-11 Medtronic Minimed, Inc. Methods and apparatuses for detecting occlusions in an ambulatory infusion pump
US7878765B2 (en) * 2005-12-02 2011-02-01 Entegris, Inc. System and method for monitoring operation of a pump

Patent Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5205819A (en) * 1989-05-11 1993-04-27 Bespak Plc Pump apparatus for biomedical use
US20080221523A1 (en) * 1998-10-29 2008-09-11 Medtronic Minimed, Inc. Methods and apparatuses for detecting occlusions in an ambulatory infusion pump
US20050211166A1 (en) * 2002-01-15 2005-09-29 Engel Harold J Pump
US20040099752A1 (en) * 2002-11-26 2004-05-27 Nordson Corporation Metered liquid dispensing system
US20050140718A1 (en) * 2003-12-25 2005-06-30 Seiko Epson Corporation Capping unit and control method for same, liquid droplet ejection apparatus and device manufacturing method
US7341327B2 (en) * 2003-12-25 2008-03-11 Seiko Epson Corporation Capping unit and control method for same, liquid droplet ejection apparatus and device manufacturing method
US7878765B2 (en) * 2005-12-02 2011-02-01 Entegris, Inc. System and method for monitoring operation of a pump
WO2008023300A1 (en) * 2006-08-21 2008-02-28 Koninklijke Philips Electronics N. V. Drug delivery device with piezoelectric actuator
US20090270834A1 (en) * 2006-08-21 2009-10-29 Koninklijke Philips Electronics N.V. Drug delivery device

Cited By (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9066748B2 (en) 2007-08-10 2015-06-30 Seiko Epson Corporation Fluid injection device
US9730723B2 (en) 2007-08-10 2017-08-15 Seiko Epson Corporation Fluid injection device
US20130218184A1 (en) * 2007-08-10 2013-08-22 Seiko Epson Corporation Fluid injection device
US8623039B2 (en) * 2007-08-10 2014-01-07 Seiko Epson Corporation Fluid injection device
US9289228B2 (en) 2007-08-10 2016-03-22 Seiko Epson Corporation Fluid injection device
US9528511B2 (en) * 2010-02-22 2016-12-27 Seiko Epson Corporation Liquid injection device
US20110208224A1 (en) * 2010-02-22 2011-08-25 Seiko Epson Corporation Liquid injection device
US9234516B2 (en) * 2010-12-24 2016-01-12 Seiko Epson Corporation Fluid ejection device and medical device
US20140301870A1 (en) * 2010-12-24 2014-10-09 Seiko Epson Corporation Fluid ejection device and medical device
US8794931B2 (en) * 2010-12-24 2014-08-05 Seiko Epson Corporation Fluid ejection device and medical device
US20120163998A1 (en) * 2010-12-24 2012-06-28 Seiko Epson Corporation Fluid ejection device and medical device
EP2783644A1 (en) * 2013-03-28 2014-10-01 Seiko Epson Corporation Fluid ejection device and medical apparatus
US20150088176A1 (en) * 2013-09-20 2015-03-26 Seiko Epson Corporation Medical apparatus system and liquid supply device
US9782194B2 (en) * 2013-09-20 2017-10-10 Seiko Epson Corporation Medical apparatus system and liquid supply device
US9610120B2 (en) 2013-10-09 2017-04-04 Olympus Corporation High-frequency treatment tool for endoscope
US10159996B2 (en) * 2014-10-20 2018-12-25 Akurate Dynamics LLC System for dispensing multiple component chemical sprays
US20160367278A1 (en) * 2014-12-24 2016-12-22 Seiko Epson Corporation Liquid ejection control device, liquid ejection system, and control method
US11014105B2 (en) 2016-10-15 2021-05-25 Akurate Dynamics, Llc Multi-segment heated hose having segment-specific heating means
US11826767B2 (en) 2020-03-16 2023-11-28 Seiko Epson Corporation Liquid ejection device

Also Published As

Publication number Publication date
JP2010106748A (ja) 2010-05-13

Similar Documents

Publication Publication Date Title
US20100111708A1 (en) Fluid ejection system, fluid ejection system drive method, and surgical apparatus
US9131952B2 (en) Fluid ejection device, fluid ejection method, and medical apparatus
JP4655163B1 (ja) 流体噴射装置、流体噴射装置の制御方法
US8623039B2 (en) Fluid injection device
JP2009045167A (ja) 流体噴射装置
EP2491875A2 (en) Fluid ejection device
US9234516B2 (en) Fluid ejection device and medical device
JP2015198859A (ja) 流体噴射装置
JP2015200287A (ja) 流体噴射装置
JP2010059792A (ja) 流体噴射装置、流体噴射ユニット、制御装置、流体噴射装置の制御方法および手術装置
US20100082054A1 (en) Fluid ejection device and fluid ejection method
EP2929846B1 (en) Surgical fluid ejection device
JP2015198861A (ja) 流体噴射装置、および、流体噴射方法
JP2010053767A (ja) 流体噴射装置、流体噴射手術器具及び流体噴射方法
US20150283809A1 (en) Fluid ejection device
JP2010059939A (ja) 流体噴射装置、流体噴射装置の制御方法および手術装置
JP2010077949A (ja) 流体噴射装置、配管部材の成形方法、流体噴射ユニット、及び手術装置
JP2015198863A (ja) 流体噴射装置
JP5636809B2 (ja) 液体噴射装置
JP2010051517A (ja) 流体噴射装置、流体噴射手術器具及び流体噴射方法
JP5776246B2 (ja) 液体噴射装置
JP5212440B2 (ja) レーザーパルスメスおよび医療機器
JP5408324B2 (ja) 流体噴射装置および医療機器
JP2010053766A (ja) 流体噴射装置、流体噴射手術器具及び流体噴射方法
JP2014013040A (ja) 流体噴射装置、流体噴射手術器具及び流体噴射方法

Legal Events

Date Code Title Description
AS Assignment

Owner name: SEIKO EPSON CORPORATION,JAPAN

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:SETO, TAKESHI;KAWASUMI, KAZUO;TABATA, KUNIO;AND OTHERS;REEL/FRAME:023432/0608

Effective date: 20090930

STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION