JP2016174892A - Liquid supply device, liquid ejection device - Google Patents

Abstract

In an apparatus for supplying liquid to a handpiece for intermittently ejecting liquid, maintenance is simplified and pulsation is reduced.
The pump includes a pump tube for supplying the liquid to a handpiece for intermittently injecting the liquid, and a tube pump for handling the pump tube for supplying the liquid. A liquid supply device in which the inner diameter of the tube is φ1.0 mm or less.
[Selection] Figure 1

Description

  The present invention relates to liquid supply.

  An apparatus for supplying liquid to a handpiece for intermittently ejecting liquid is known (Patent Document 1). The liquid supply device disclosed in Patent Document 1 includes two plunger pumps. The pulsation of the supplied liquid is reduced by the two plunger pumps supplying the liquid alternately.

JP 2014-95353 A

  In the case of the above prior art, it takes time to maintain the plunger pump. In particular, when used for medical purposes, replacement and sterilization may be required, which is a particular problem. In view of the above-described prior art, the present invention has an object to solve the problem of suppressing the pressure fluctuation of the supplied liquid with a mechanism that is easy to maintain.

  SUMMARY An advantage of some aspects of the invention is to solve the above-described problems, and the invention can be implemented as the following forms.

  According to one aspect of the present invention, a liquid supply apparatus is provided. The liquid supply apparatus includes: a pump tube for supplying the liquid to a hand piece for intermittently ejecting liquid; and a tube pump for handling the pump tube for supplying the liquid; The inner diameter of the pump tube is φ1.0 mm or less. According to this form, the pulsation of the liquid supplied to the handpiece can be suppressed. When the pump tube has a small inner diameter (φ1.0 mm or less), the number of rotations of the tube pump can be increased even when the pump tube is supplied at the same flow rate as when the pump tube has a large inner diameter. For this reason, the pressure fluctuation downstream of the pump tube is suppressed. Furthermore, the pump tube and the tube pump are easy to maintain.

  In the above embodiment, the inner diameter of the pump tube may be φ0.8 mm or less. According to this embodiment, the pressure fluctuation can be further suppressed.

  In the above embodiment, the inner diameter of the pump tube may be 0.5 mm or less. According to this embodiment, the pressure fluctuation can be further suppressed.

  In the above embodiment, the inner diameter of the pump tube may be 0.5 mm or more. According to this aspect, the rotation speed of the pump tube for securing a predetermined flow rate does not become too large, so that the durability of the tube pump is improved.

  In the above aspect, the roller frequency of the tube pump may be 3.84 Hz or more. According to this embodiment, the flow rate can be secured even if the inner diameter of the pump tube is thin.

  In the above embodiment, the roller frequency may be 6.56 Hz or more. According to this embodiment, the flow rate can be secured even if the inner diameter of the pump tube is thin.

  In the above embodiment, the roller frequency may be 12.8 Hz or more. According to this embodiment, the flow rate can be secured even if the inner diameter of the pump tube is further narrowed.

  The said form WHEREIN: The wall thickness of the said pump tube may be 1.6 mm or more. According to this aspect, since the deformation of the pump tube is suppressed when the roller in contact with the pump tube is switched, it is possible to suppress the pressure downstream of the pump tube from rapidly decreasing.

  In the above form, the handpiece is a surgical excision instrument; the supply flow rate by the tube pump may be not less than 3 ml / min and not more than 10 ml / min. According to this embodiment, a flow rate suitable for excision by intermittent liquid injection can be supplied.

  The present invention can be realized in various forms other than the above. For example, it can be realized as a liquid ejecting apparatus including the hand piece and the liquid supply apparatus.

FIG. 2 is a schematic configuration diagram of a liquid ejecting apparatus. The perspective view of a handpiece (mounted state). The perspective view of a handpiece (separated state). The perspective view which shows a nozzle unit. Sectional drawing which shows a handpiece. The expanded sectional view of a joint part and an actuator unit (mounting state). The expanded sectional view of a joint part and an actuator unit (separated state). FIG. 4 is an enlarged cross-sectional view around the liquid chamber (mounted state). The expanded sectional view of the liquid chamber vicinity (separated state). The figure about the welding of a liquid chamber side diaphragm and a drive side diaphragm. The graph which shows the relationship between flow volume and motor rotation speed. A graph (φ1.6 mm) showing the experimental results of the injection pressure and the pressure in the tube. A graph (φ0.8mm) which shows an experimental result of injection pressure and pressure in a tube. A graph (.phi.0.5 mm) showing experimental results of injection pressure and tube pressure. A graph (φ1.6 mm) showing the experimental results of the injection pressure and the pressure in the tube. A graph (φ0.8mm) which shows an experimental result of injection pressure and pressure in a tube. A graph (.phi.0.5 mm) showing experimental results of injection pressure and tube pressure. Graph (φ1.1 mm) showing the experimental results of jet load and tube pressure. Graph (φ1.0 mm) showing the experimental results of jet load and tube pressure. A graph (φ0.8mm) which shows an experimental result of jet load and pressure in a tube.

  First, an outline of the liquid ejecting apparatus 20 will be described with reference to FIGS. 1 to 10 to describe a liquid ejecting mechanism and a suction mechanism.

  FIG. 1 schematically shows the configuration of the liquid ejecting apparatus 20. The liquid ejecting apparatus 20 is a medical device used in a medical institution, and has a function of excising an affected part by ejecting liquid onto the affected part.

  The liquid ejecting apparatus 20 includes a control unit 30, an actuator cable 31, a pump cable 32, a foot switch 35, a suction device 40, a suction tube 41, a liquid supply device 50, and a handpiece 100 (operation unit). With.

  The liquid supply device 50 includes a water supply bag 51, a spike needle 52, first to fifth connectors 53a to 53e, first to fourth water supply tubes 54a to 54d, a pump tube 55, a blockage detection mechanism 56, And a filter 57. The handpiece 100 includes a nozzle unit 200 and an actuator unit 300. The nozzle unit 200 includes an ejection tube 205 and a suction tube 400.

  The water supply bag 51 is made of a transparent synthetic resin, and is filled with a liquid (specifically, physiological saline). In addition, in this application, even if it fills with liquids other than water, it calls the water supply bag 51. FIG. The spike needle 52 is connected to the first water supply tube 54a via the first connector 53a. When the spike needle 52 is stabbed into the water supply bag 51, the liquid filled in the water supply bag 51 can be supplied to the first water supply tube 54a.

  The first water supply tube 54a is connected to the pump tube 55 via the second connector 53b. The pump tube 55 is connected to the second water supply tube 54b via the third connector 53c. The tube pump 60 sandwiches the pump tube 55 between the stator and the rotor. The tube pump 60 handles the pump tube 55 by rotating a plurality of rollers by rotation of a built-in motor. By being handled in this way, the liquid in the pump tube 55 is sent out from the first water supply tube 54a side to the second water supply tube 54b side.

  The blockage detection mechanism 56 detects the blockages in the first to fourth water supply tubes 54a to 54d by measuring the pressure in the second water supply tube 54b.

  The second water supply tube 54b is connected to the third water supply tube 54c via the fourth connector 53d. A filter 57 is connected to the third water supply tube 54c. The filter 57 collects foreign matters contained in the liquid.

  The third water supply tube 54c is connected to the fourth water supply tube 54d through the fifth connector 53e. The fourth water supply tube 54d is connected to the handpiece 100. The liquid supplied to the handpiece 100 through the fourth water supply tube 54d is intermittently ejected from the nozzle 207 provided at the tip of the ejection tube 205 by driving the actuator unit 300. In this way, the liquid is intermittently ejected, so that the resecting capability can be secured with a small flow rate.

  The injection tube 205 and the suction tube 400 constitute a double tube having the injection tube 205 as an inner tube and the suction tube 400 as an outer tube. The suction tube 41 is connected to the nozzle unit 200. The suction device 40 sucks the inside of the suction tube 400 through the suction tube 41. By this suction, liquid near the tip of the suction tube 400, a cut piece, and the like are sucked.

  The control unit 30 controls the tube pump 60 and the actuator unit 300. Specifically, the control unit 30 transmits a drive signal via the actuator cable 31 and the pump cable 32 while the foot switch 35 is depressed. The drive signal transmitted via the actuator cable 31 drives the actuator unit 300. The drive signal transmitted via the pump cable 32 drives the tube pump 60. Therefore, the liquid is intermittently ejected while the user steps on the foot switch 35, and the liquid ejection stops while the user does not step on the foot switch 35.

  2 and 3 are perspective views of the handpiece 100. FIG. FIG. 2 shows a state where the actuator unit 300 is attached to the nozzle unit 200 (hereinafter referred to as “attached state”). FIG. 3 shows a state where the actuator unit 300 and the nozzle unit 200 are separated (hereinafter referred to as “separated state”).

  The actuator unit 300 is configured to be detachable from the nozzle unit 200. The actuator unit 300 is attached to the nozzle unit 200, and the actuator unit 300 and the nozzle unit 200 are integrated to function as the handpiece 100.

  Since the liquid flows through the nozzle unit 200, the nozzle unit 200 is replaced every operation. Further, among the components included in the liquid supply device 50, the ones in which the liquid flows (water supply bag 51, first to fourth water supply tubes 54a to 54d, pump tube 55, etc.) are replaced for each operation. Since the actuator unit 300 does not touch the liquid, it can be used in a plurality of operations by performing a sterilization process or a cleaning process.

  The nozzle unit 200 includes a handpiece case 210, a joint portion 250, and a suction force adjusting mechanism 500 in addition to the above-described injection tube 205 and suction tube 400. The handpiece case 210 has a function as a grip held by the user and a function of holding the flow path inside. This flow path is a flow path through which the liquid to be ejected and the liquid to be sucked flow as described above.

  The suction force adjustment mechanism 500 is provided in the handpiece 100 and includes a hole 522. When the opening area of the hole 522 changes, the suction force by the suction pipe 400 changes (detailed with FIG. 5). The joint part 250 is a part for attaching / detaching the actuator unit 300 to / from the nozzle unit 200.

  The actuator unit 300 includes a connecting part 310 and a driving part 350. The connecting portion 310 mechanically and electrically connects the actuator cable 31 and the drive portion 350. The driving unit 350 generates a driving force for intermittently ejecting the liquid.

  FIG. 4 is a perspective view showing the nozzle unit 200. FIG. 4 shows a state in which the suction tube 400 is removed from the handpiece case 210. The handpiece 100 may be used with the suction tube 400 removed. In a state where the suction tube 400 is removed, suction using the suction tube 400 is not possible, but liquid can be ejected from the ejection tube 205.

  The suction tube 400 includes a convex portion 410. The convex part 410 is a part for attaching the suction tube 400 to the handpiece case 210.

  As described with FIG. 1, the fourth water supply tube 54 d is connected to the handpiece case 210. 2 and 3 do not show the fourth water supply tube 54d because of the line of sight.

  FIG. 5 is a cross-sectional view showing the handpiece 100. The fourth water supply tube 54d is bent in a U shape inside the handpiece case 210 and connected to the inlet channel 241. The inlet channel 241 communicates with the ejection pipe 205 via the liquid chamber 240 (see FIGS. 8 and 9).

  The channel diameter of the inlet channel 241 is smaller than the channel diameter of the injection pipe 205. For this reason, even if the pressure in the liquid chamber 240 fluctuates (described later), the liquid in the liquid chamber 240 is prevented from flowing back into the inlet channel 241.

  The handpiece case 210 includes a recess 211 at the tip. The attachment of the suction pipe 400 is realized by fitting the convex portion 410 into the concave portion 211. The attached suction tube 400 communicates with the suction flow path section 230. The suction flow path unit 230 is connected to the suction tube 41 via the suction force adjustment mechanism 500.

  The user can adjust the suction force by the suction pipe 400 using the hole 522. Specifically, if the area where the hole 522 is opened is reduced, the flow rate of air flowing in from the hole 522 is also reduced, so that the flow rate of fluid (air, liquid, etc.) sucked through the suction pipe 400 is reduced. growing. That is, the suction force by the suction pipe 400 is increased. On the contrary, if the area where the hole 522 is opened is increased, the flow rate of the air flowing from the hole 522 is also increased, so that the suction force by the suction pipe 400 is reduced. Usually, the user adjusts the open area of the hole 522 by adjusting the area where the hole 522 is closed by the thumb. In a state where the hole 522 is not covered at all, the shape of the hole 522 is designed so that the suction force by the suction pipe 400 becomes minute or no suction force acts. In this embodiment, although the flow area of the suction pipe 400 is larger than the opening area of the hole 522, the flow resistance of the suction pipe 400 is reduced by making the length of the suction pipe 400 longer than the length of the hole 522. It is larger than the flow path resistance. In this way, when the hole 522 is not covered at all, the suction force by the suction tube 400 can be made minute.

  As shown in FIG. 5, the longitudinal direction is defined with respect to the handpiece case 210. The longitudinal direction is a direction included in the cross section shown in FIG. 5 and is a horizontal direction in a predetermined posture. The predetermined posture is a posture when the user holds the handpiece 100 with the hand after the palm is turned up. The longitudinal direction in the present embodiment matches the flow path direction of the suction flow path section 230. The flow path direction of the suction flow path section 230 is a flow direction in the suction flow path section 230 at a portion where the suction flow path section 230 is in contact with the suction force adjustment mechanism 500.

  6 and 7 are enlarged sectional views showing the vicinity of the joint portion 250 and the actuator unit 300. FIG. FIG. 6 shows a mounted state. FIG. 7 shows a separated state.

  The drive unit 350 includes a housing 351, a fixed member 353, a piezoelectric element 360, and a movable plate 361. The housing 351 is a cylindrical member. The movable plate 361 includes a piston 362 and a drive side diaphragm 364.

  The piezoelectric element 360 is a stacked piezoelectric element. The piezoelectric element 360 is disposed in the housing 351 so that the extending and contracting direction is along the longitudinal direction of the housing 351. The piezoelectric element 360 in the present embodiment has a substantially regular quadrangular prism shape, is 3.5 mm square, and has a height of 18 mm.

  The fixing member 353 is fixed to one end of the housing 351. The piezoelectric element 360 is fixed to the fixing member 353 with an adhesive.

  The material of the drive side diaphragm 364 is a metal, specifically stainless steel, and more specifically SUS304 or SUS316L. The drive side diaphragm 364 is formed thicker (for example, 300 μm) in order to preload the piezoelectric element 360 (described later). Further, since the piezoelectric element 360 is made of metal and is formed thick, it is smoothly curved when pushed by the piston 362. For this reason, the liquid chamber side diaphragm 260 can also be smoothly deformed in the mounted state.

  The drive side diaphragm 364 is disposed so as to cover the other end of the housing 351 and is fixed to the housing 351 by welding.

  The piston 362 is fixed to one end of the piezoelectric element 360 with an adhesive, and is disposed so as to contact the drive side diaphragm 364. The piston 362 has a shape in which cylinders having different diameters are stacked as concentric circles. The smaller diameter is in contact with the drive side diaphragm 364. For this reason, the drive side diaphragm 364 is not pushed toward the end, and a large force does not act on the welded portion. The piston 362 and the drive side diaphragm 364 are not fixed by an adhesive or the like but are only in contact with each other.

  A male screw portion 351 a is provided on the outer periphery of the housing 351. The transition from the separated state to the mounted state is realized by tightening the male screw portion 351a to the female screw portion 253 provided in the joint portion 250.

  The connecting portion 310 includes a first case 311, a second case 312, a third case 313, a holding member 314, a metal plate 315, a first screw 316, a second screw 317, and a third screw 318. Is provided. Note that the metal plate 315 can also be referred to as the relay substrate 315.

  The first case 311 is fixed to the fixing member 353 by the first screw 316. The second case 312 is fixed to the first case 311 by a second screw 317 and a third screw 318. The two metal plates 315 are inserted (accommodated) in the first case 311.

  The holding member 314 is fixed by being crimped near the end of the actuator cable 31. The third case 313 is a member for connecting the second case 312 and the holding member 314. The third case 313 is fixed to the second case 312 in a state where the portion where the outer diameter of the holding member 314 is expanded is hooked.

  The actuator cable 31 is connected to the two metal plates 315 in a state of being fixed as described above. The metal plate 315 is connected to the positive electrode and the negative electrode of the piezoelectric element 360 by wiring (not shown).

  The piezoelectric element 360 expands and contracts according to a drive signal input via the actuator cable 31, the metal plate 315, and the above wiring. When the piezoelectric element 360 expands and contracts, the piston 362 vibrates in the longitudinal direction of the piezoelectric element 360. When the piston 362 vibrates, the drive side diaphragm 364 is deformed following the vibration.

  The piezoelectric element 360 is assembled in a preloaded state in order to appropriately perform expansion and contraction. The preloaded state is a state in which the piezoelectric element 360 is pressed toward the driving diaphragm 364 and the piezoelectric element 360 is compressed in the expansion / contraction direction. The preload load is 10 to 50% of the maximum generated force of the piezoelectric element 360, specifically 40 to 200N. For this reason, even when a drive signal is not input to the piezoelectric element 360, the drive side diaphragm 364 receives force from the piezoelectric element 360 via the piston 362. The reason that the drive side diaphragm 364 is made of metal and is thicker than the liquid chamber side diaphragm 260 is to hold the preload.

  Since the driving side diaphragm 364 is deformed as described above, the driving side diaphragm 364 can be deformed following the contraction of the piezoelectric element 360 without being bonded to the piston 362.

  8 and 9 are cross-sectional views showing the vicinity of the liquid chamber 240 in an enlarged manner. FIG. 8 shows a mounted state. FIG. 9 shows the separated state.

  A liquid chamber 240 is provided inside the joint portion 250. The liquid chamber 240 is formed by covering the recess 244 with the liquid chamber side diaphragm 260. The recess 244 is a portion that is thin and circularly recessed in the joint portion 250. The liquid chamber side diaphragm 260 is formed thinner than the drive side diaphragm 364 (for example, 50 to 100 μm) so as to be easily deformed according to the expansion and contraction of the piezoelectric element 360. The liquid chamber side diaphragm 260 has a diameter of 13 to 15 mm, and is fixed to the joint portion 250 by welding. The welding position is shown as welding Y1 shown in FIG. The material of the liquid chamber side diaphragm 260 is a metal, specifically stainless steel, and more specifically SUS304 or SUS316L.

  As shown in FIG. 8, the liquid chamber side diaphragm 260 and the drive side diaphragm 364 are in contact with each other in the mounted state. For this reason, as described above, when the driving side diaphragm 364 is deformed, the liquid chamber side diaphragm 260 is similarly deformed.

  When the drive side diaphragm 364 is deformed, the volume of the liquid chamber 240 changes. Due to this variation, the pressure of the liquid filled in the liquid chamber 240 varies. When the pressure in the liquid chamber 240 decreases, the liquid flows into the liquid chamber 240 from the inlet channel 241. When the pressure in the liquid chamber 240 increases, the liquid flows out from the liquid chamber 240 to the ejection pipe 205. The liquid that has flowed out to the ejection tube 205 is ejected from the tip of the ejection tube 205. Since the pressure in the liquid chamber 240 rises intermittently, the liquid is ejected from the ejection pipe 205 intermittently.

  As described above, the liquid chamber side diaphragm 260 and the drive side diaphragm 364 are integrally deformed. That is, the liquid chamber side diaphragm 260 and the movable plate 361 are integrally deformed. Reference numeral 460 shown in FIG. 8 indicates a composite diaphragm 460 in which the liquid chamber side diaphragm 260 and the movable plate 361 that are integrally deformed in this manner are combined. The composite diaphragm 460 can be regarded as one diaphragm in the mounted state.

  FIG. 10 is a diagram for explaining the welding of the liquid chamber side diaphragm 260 and the driving side diaphragm 364. The housing 351 is provided with a chamfer 351b as shown in FIG. The chamfer 351b is provided so that the weld Y1 that fixes the liquid chamber side diaphragm 260 and the housing 351 do not interfere with each other.

  As shown in FIG. 10, the front end of the housing 351 is retracted by a dimension C from the front end of the drive side diaphragm 364. As a result, a clearance is generated between the liquid chamber side diaphragm 260 and the housing 351 in the mounted state. By performing welding so that the weld mark of the weld Y2 that fixes the drive side diaphragm 364 is located in this clearance, interference between the weld Y2 and the liquid chamber side diaphragm 260 is avoided.

  The code | symbol 255 shown by FIG. 10 shows the escape part 255 provided in another form. In this embodiment, as shown in FIG. 8, FIG. 9, etc., the escape part 255 is not provided. The relief portion 255 is a portion of the inner periphery of the joint portion 250 where the wall is sunk toward the inside. By providing the relief portion 255, the internal thread portion 253 can be easily processed.

  Hereinafter, the influence of the inner diameter of the pump tube 55 will be described.

  FIG. 11 is a graph showing the relationship between the liquid flow rate (ml / min) and the motor rotation speed (rpm) of the tube pump 60. FIG. 11 shows the case where the inner diameter of the pump tube 55 is φ1.6 mm, φ0.8 mm, and φ0.5 mm.

  The wall thickness of the pump tube 55 in the present embodiment is 1.6 mm regardless of the above-mentioned inner diameter. Since the pump tube 55 has a thick wall thickness (1.6 mm), deformation due to rapid pressure fluctuation in the pump tube 55 is suppressed. The sudden pressure fluctuation in the pump tube 55 occurs, for example, when the roller that contacts the pump tube 55 is switched.

  Since the tube pump 60 in the present embodiment includes four rollers, the roller frequency is four times the motor rotation frequency. The roller frequency is a frequency at which the liquid is sucked and discharged, and is calculated by the product of the motor rotation frequency and the number of rollers. Thus, since the roller frequency has a one-to-one correspondence with the motor rotation number, the value converted into the roller frequency is also shown in FIG. 11 as the second horizontal axis.

  As shown in FIG. 11, when compared at the same rotation speed, the smaller the inner diameter of the pump tube 55, the smaller the flow rate. Therefore, in order to secure the flow rate while reducing the inner diameter of the pump tube 55, the motor rotational speed may be increased.

  In this embodiment, the flow rate is set to 4 ml / min. In the case of the present embodiment, since the liquid is intermittently ejected, sufficient excision ability can be secured with such a small flow rate. In order to secure this flow rate, it may be set to 30 rpm for φ1.6 mm, 98.4 rpm for φ0.8 mm, and 192 rpm for φ0.5 mm.

  12-17 is a graph which shows the experimental result about the relationship between injection pressure (MPa), the pressure in a tube (MPa), and time (second). 15 to 17 show an enlarged vicinity of the peak of the injection pressure.

  The ejection pressure is the pressure of the liquid ejected from the tip of the ejection pipe 205. The tube internal pressure is a pressure downstream of the pump tube 55 and upstream of the liquid chamber 240. In the present embodiment, the pressure in the fourth water supply tube 54d was measured.

  12 and 15 show the case where the inner diameter of the pump tube 55 is φ1.6 mm, FIGS. 13 and 16 show the case where the inner diameter of the pump tube 55 is φ0.8 mm, and FIGS. 14 and 17 show the inner diameter of the pump tube 55. The case of φ0.5mm is shown.

  In this experiment, the frequency of the drive signal applied to the piezoelectric element 360 was set to 400 Hz, and the maximum voltage was set to 35V. In this experiment, in order to set the flow rate to 4 ml / min as described above, 30 rpm was set for φ1.6 mm, 98.4 rpm was set for φ0.8 mm, and 192 rpm was set for φ0.5 mm. Since 30 rpm is 0.5 revolutions per second, the roller frequency is 2.0 Hz. Since 98.4 rpm is 1.64 revolutions per second, the roller frequency is 6.56 Hz. Since 192 rpm is 3.2 revolutions per second, the roller frequency is 12.8 Hz.

  As shown in FIGS. 12 and 15, when the inner diameter of the pump tube 55 is φ1.6 mm, the pressure in the tube has a long fluctuation cycle and a large fluctuation width of about ± 16%. This is considered due to the fact that the inner diameter of the pump tube 55 is large (φ1.6 mm). That is, if the pump tube 55 is thick, the amount of water supplied at one time by each roller increases. For this reason, in order to satisfy the demand for the supply flow rate, the roller frequency is lowered (2.0 Hz). As a result, the pressure in the tube greatly fluctuates in a long cycle.

  In addition, when the inner diameter of the pump tube 55 is φ1.6 mm, the maximum value of the injection pressure is not stable. This is considered to be influenced by the large fluctuation range of the pressure in the tube.

  On the other hand, as shown in FIGS. 13 and 16, when the inner diameter of the pump tube 55 is φ0.8 mm, it is thinner than the case of φ1.6 mm, so the roller frequency is increased (6.56 Hz). As a result, the fluctuation cycle of the pressure in the tube becomes shorter and the fluctuation width becomes smaller (about ± 6%). Along with this, when the inner diameter of the pump tube 55 is φ0.8 mm, the maximum value of the injection pressure is more stable than when the inner diameter of the pump tube 55 is φ1.6 mm.

  Further, as shown in FIGS. 14 and 17, when the inner diameter of the pump tube 55 is φ0.5 mm, the fluctuation cycle of the pressure in the tube is shorter and the fluctuation width is smaller than the case where the inner diameter is φ0.8 mm. (About ± 4%). In addition, the maximum value of the injection pressure is more stable when the inner diameter of the pump tube 55 is φ0.5 mm than when the inner diameter of the pump tube 55 is φ0.8 mm.

  As described above, even in the liquid supply mechanism using the pump tube 55 and the tube pump 60, the fluctuation of the pressure in the tube can be reduced and the maximum value of the injection pressure can be stabilized. Further, with this liquid supply mechanism, maintenance is easy. The pump tube 55 is easy to replace and inexpensive. The tube pump 60 can be reused because it does not touch the liquid.

  When the inner diameter of the pump tube 55 is φ0.5 mm or more, for example, in the case of φ0.5 mm or φ0.8 mm, the roller frequency for securing the same supply flow rate is smaller than in the case of less than φ0.5 mm. As a result, the motor speed of the tube pump 60 can be reduced. For this reason, when the inner diameter of the pump tube 55 is φ0.5 mm or more, it is preferable for the durability of the tube pump 60 as compared with the case where the inner diameter is less than φ0.5 mm. In addition, since the pump tube 55 is disposable, in this embodiment, durability hardly poses a problem.

  18, 19 and 20 are graphs showing experimental results on the relationship between jet load (mN), tube pressure (MPa), and time (seconds).

  The jet load (mN) is an impact force caused by liquid ejected intermittently. In the present embodiment, a value measured by a force sensor arranged at a predetermined distance from the tip of the nozzle 207 is defined as a jet load.

  18 shows a case where the inner diameter of the pump tube 55 is φ1.1 mm (hereinafter, “the inner diameter of the pump tube 55 is omitted when the numerical value of the inner diameter is shown), FIG. 19 shows a case where the inner diameter is 1.0 mm, and FIG. The case of .8 mm is shown.

  The number of rotations of the tube pump 60 was set to 55.2 rpm for φ1.1 mm, 57.6 rpm for φ1.0 mm, and 86.4 rpm for φ0.8 mm. In terms of the roller frequency, it is 3.68 Hz for φ1.1 mm, 3.84 Hz for φ1.0 mm, and 5.76 Hz for φ0.8 mm.

  The results of statistical processing on the pressure data in the tube obtained by the experiment are as follows. In addition, in subsequent statistical processing, in addition to the data of 0 second-0.5 second shown on the graph, the data of 0.5 second-1.0 second were also included.

In the case of φ1.1 mm, the average value was 51.0 × 10 ⁻³ MPa, the standard deviation was 1.4 × 10 ⁻³ MPa, the maximum value was 53.4 × 10 ⁻³ MPa, and the minimum value was 47.1 × 10 ⁻³ MPa.

In the case of φ1.0 mm, the average value was 49.7 × 10 ⁻³ MPa, the standard deviation was 1.5 × 10 ⁻³ MPa, the maximum value was 52.9 × 10 ⁻³ MPa, and the minimum value was 46.2 × 10 ⁻³ MPa.

In the case of φ0.8 mm, the average value was 48.1 × 10 ⁻³ MPa, the standard deviation was 1.1 × 10 ⁻³ MPa, the maximum value was 50.2 × 10 ⁻³ MPa, and the minimum value was 45.1 × 10 ⁻³ MPa.

  As described above, the standard deviation of the pressure in the tube is smaller in the case of φ0.8 mm than in the case of φ1.0 mm and φ1.1 mm. Therefore, φ0.8 mm is preferable compared to φ1.0 mm and φ1.1 mm. As a result, the roller frequency of 5.76 Hz in the case of φ0.8 mm is more preferable than 3.68 Hz in the case of φ1.1 mm and 3.84 Hz in the case of φ1.0 mm.

  The results of statistical processing on the jet load data obtained by the experiment are as follows.

  In the case of φ1.1 mm, the average value was 0.72 mN, the standard deviation was 0.019 mN, the maximum value was 0.76 mN, and the minimum value was 0.67 mN.

  In the case of φ1.0 mm, the average value was 0.71 mN, the standard deviation was 0.017 mN, the maximum value was 0.75 mN, and the minimum value was 0.66 mN.

  In the case of φ0.8 mm, the average value was 0.70 mN, the standard deviation was 0.012 mN, the maximum value was 0.72 mN, and the minimum value was 0.67 mN.

  As described above, the standard deviation of the jet load is smaller in the case of φ1.0 mm than in the case of φ1.1 mm. That is, the jet load is stabilized. Therefore, φ1.0 mm is preferable compared to φ1.1 mm. As a result, the roller frequency of 3.84 Hz in the case of φ1.0 mm is more preferable than 3.68 Hz in the case of φ1.1 mm.

  As described above, the standard deviation of the jet load is smaller in the case of φ0.8 mm than in the case of φ1.0 mm. Therefore, φ0.8 mm is preferable compared to φ1.0 mm. As a result, the roller frequency of 5.76 Hz in the case of φ0.8 mm is more preferable than 3.84 Hz in the case of φ1.0 mm.

  The present invention is not limited to the embodiments, examples, and modifications of the present specification, and can be implemented with various configurations without departing from the spirit of the present invention. For example, the technical features in the embodiments, examples, and modifications corresponding to the technical features in the embodiments described in the summary section of the invention are to solve some or all of the above-described problems, or In order to achieve part or all of the effects described above, replacement or combination can be performed as appropriate. If the technical feature is not described as essential in this specification, it can be deleted as appropriate. For example, the following are exemplified.

The inner diameter of the pump tube may be smaller than φ0.5 mm.
The roller frequency of the tube pump may be larger than 12.8 Hz, smaller than 6.56 Hz, or smaller than 3.84 Hz.
The supply flow rate by the tube pump may be, for example, 3 ml / min or more and 10 ml / min or less. Alternatively, other values may be used.
The wall thickness of the pump tube may be thicker than 1.6 mm or thinner than 1.6 mm.

  The number of rollers provided in the tube pump may be other than four, for example, three. When the number of rollers is changed, the number of rotations of the motor may be adjusted in order to maintain the roller frequency.

The nozzle unit and the actuator unit may be integrally formed.
The nozzle unit may be used multiple times by sterilization.
The liquid to be ejected may be pure water or a chemical solution.
The liquid ejecting apparatus may be used other than medical equipment.
For example, the liquid ejecting apparatus may be used in a cleaning apparatus that removes dirt with the ejected liquid, or may be used in a drawing apparatus that draws a line or the like with the ejected liquid.

  In the embodiment, a configuration using a piezoelectric element as an actuator is employed. However, a configuration in which liquid is ejected using an optical maser, or a configuration in which liquid is pressurized by a pump or the like and liquid is ejected may be employed. The structure in which the liquid is ejected using the optical maser is a structure in which bubbles are generated in the liquid by irradiating the liquid with the optical maser, and the liquid pressure rise caused by the generation of the bubbles is utilized.

In the embodiment, the configuration in which the liquid is intermittently ejected is employed, but a configuration having a function of ejecting the liquid continuously may be employed. For example, the structure which can selectively use intermittent injection and continuous injection may be sufficient. In order to perform continuous injection using the hardware configuration of the embodiment, only the tube pump may be driven with the driving of the actuator stopped or reduced. In this configuration, intermittent spraying may be performed for excision and continuous spraying may be performed for cleaning.
Or the structure which can implement only continuous injection may be sufficient. In the case of this configuration, the ablation may be performed by continuous injection.

DESCRIPTION OF SYMBOLS 20 ... Liquid injection apparatus, 30 ... Control part, 31 ... Actuator cable, 32 ... Pump cable, 35 ... Foot switch, 40 ... Suction apparatus, 41 ... Suction tube, 50 ... Liquid supply apparatus, 51 ... Water supply bag, 52 ... spike needle, 53a ... first connector, 53b ... second connector, 53c ... third connector, 53d ... fourth connector, 53e ... fifth connector, 54a ... first water supply tube, 54b ... second water supply tube, 54c ... 3rd water supply tube, 54d ... 4th water supply tube, 55 ... Pump tube, 56 ... Blockage detection mechanism, 57 ... Filter, 60 ... Tube pump, 100 ... Handpiece, 200 ... Nozzle unit, 205 ... Injection pipe, 207 ... Nozzle , 210 ... hand piece case, 211 ... recess, 230 ... suction channel part, 240 ... liquid chamber 241 ... Inlet flow path, 244 ... depression, 250 ... joint part, 253 ... female screw part, 255 ... relief part, 260 ... liquid chamber side diaphragm, 300 ... actuator unit, 310 ... coupling part, 311 ... first case, 312 2nd case, 313 ... 3rd case, 314 ... Holding member, 315 ... Metal plate, 316 ... 1st screw, 317 ... 2nd screw, 318 ... 3rd screw, 350 ... Drive part, 350a ... Drive part, 351 ... housing, 351a ... male screw part, 353 ... fixing member, 360 ... piezoelectric element, 361 ... movable plate, 362 ... piston, 364 ... drive side diaphragm, 370 ... adhesive containing hard material, 371 ... adhesive, 372 ... hard 400, suction pipe, 410, convex portion, 460, synthetic diaphragm, 500, suction force adjusting mechanism, 522, hole

Claims (10)

A pump tube for supplying the liquid to a handpiece for intermittently ejecting the liquid;
A tube pump for handling the pump tube to supply the liquid;
An inner diameter of the pump tube is φ1.0 mm or less. The liquid supply apparatus according to claim 1, wherein an inner diameter of the pump tube is φ0.8 mm or less. The liquid supply apparatus according to claim 1, wherein an inner diameter of the pump tube is 0.5 mm or less. The liquid supply device according to claim 1, wherein an inner diameter of the pump tube is φ0.5 mm or more. The liquid supply apparatus according to any one of claims 1 to 4, wherein a roller frequency of the tube pump is 3.84 Hz or more. The liquid supply apparatus according to claim 5, wherein the roller frequency is 6.56 Hz or more. The liquid supply apparatus according to claim 6, wherein the roller frequency is 12.8 Hz or more. The liquid supply apparatus according to any one of claims 1 to 7, wherein a wall thickness of the pump tube is 1.6 mm or more. The handpiece is a surgical resection instrument;
The liquid supply apparatus according to any one of claims 1 to 8, wherein a supply flow rate by the tube pump is 3 ml / min or more and 10 ml / min or less.   A liquid ejecting apparatus comprising the handpiece according to claim 1 and the liquid supply apparatus.

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