JP5621599B2 - Liquid ejecting apparatus and medical device - Google Patents

Description

  The present invention relates to a liquid ejecting apparatus and a medical device.

  In recent years, a surgical technique has been developed in which a liquid such as water or physiological saline is pressurized and sprayed onto the affected tissue site during surgery to excise the affected tissue site with the pressure of the liquid. In the liquid ejecting apparatus used for such an operation, the liquid is ejected from an ejection port provided at the tip of the nozzle, and the operator ejects the liquid toward the affected tissue site by the nozzle ejection port. It is possible to excise the affected tissue site.

  Further, in the water jet surgical apparatus that excises the affected tissue site by injecting pressurized water, the pressurized gas injected together with the pressurized water removes the pressurized water that hits the affected tissue site, and the pressurized water is applied to the affected tissue site in the firing state. There has been proposed a water jet surgical apparatus that prevents accumulation and, as a result, can effectively apply pressurized water to an affected tissue site (see, for example, Patent Document 1).

JP-A-6-192

  However, in the technique of Patent Document 1, since the pressurized gas is injected in a state surrounding the periphery of the pressurized water, when the pressure of the pressurized water is low, the injection direction of the pressurized water is easily affected by the pressurized gas, and the excision is performed. There was a risk of misalignment at the location. In addition, when pressurized water is jetted in a pulsed manner, it is particularly susceptible to great influences, and there is a risk that displacement will occur at the excision site.

  SUMMARY An advantage of some aspects of the invention is to solve at least a part of the problems described above, and the invention can be implemented as the following forms or application examples.

  Application Example 1 A liquid chamber including a liquid chamber whose volume can be changed, an inlet channel and an outlet channel communicating with the liquid chamber, a volume changing unit that changes the volume of the liquid chamber, and a liquid ejection opening. A liquid injection pipe for injecting gas, a cooling section for cooling the gas, a gas injection pipe which is disposed on an outer periphery of the liquid injection pipe and includes a gas injection opening, and which injects the cooling gas cooled by the cooling section; The liquid ejecting apparatus is characterized in that a guiding surface for guiding an ejection direction of the cooling gas ejected from the gas ejecting pipe is formed in the liquid ejecting pipe.

  As a result, the affected tissue site is cooled with the cooled cooling gas, so that the difference in strength that differs from site to site can be made closer, so the excisable stress (cutting force) becomes almost uniform, and cutting It becomes easy to control the depth. In addition, since the affected tissue site is cooled, the generation of body fluid such as blood accompanying the cutting is extremely reduced, and the affected tissue site can be easily seen. Further, since the affected tissue part is cooled, the elasticity of the affected part tissue part is weakened and the excision part can be cut deeply, so that the liquid used for cutting can be reduced.

  Application Example 2 In the liquid ejecting apparatus, a gas that adjusts an ejection direction of the cooling gas according to a distance between the liquid ejection opening and an ejection target from which the liquid is ejected from the liquid ejection opening. A liquid ejecting apparatus comprising an ejection adjusting unit.

  According to this, since the spread of the cooled cooling gas can be adjusted, the cooled cooling gas can be adjusted to the region where it hits the excision site. Furthermore, even if the attenuation of the wind pressure of the cooled cooling gas is increased by increasing the distance between the gas injection opening and the excision location, by increasing the injection amount of the cooled cooling gas, It is possible to suppress a decrease in the wind pressure that reaches.

  Application Example 3 In the liquid ejecting apparatus, the outer diameter of the liquid ejecting tube is a shape that widens toward the tip, and the cooling gas is guided along the outer wall of the liquid ejecting opening. A liquid ejecting apparatus.

  According to this, it is possible to guide the cooled cooling gas along the outer wall of the liquid ejection opening to the excision site and improve the excision ability.

  Application Example 4 The liquid ejecting apparatus according to the application example, further including a temperature measuring mechanism that measures a temperature of an ejection target from which the liquid is ejected from the liquid ejecting opening.

  According to this, the cutting force (cutting stress) at the excision location has a correlation with the temperature at the excision location, so it is possible to grasp the surface temperature of the location where the liquid comes into contact and check whether it can be excised before liquid injection. In addition, the strength of the liquid jetting and the cooling temperature of the cooling unit can be controlled according to the temperature of the excision site.

  In addition, by automatically controlling the strength of the jet according to the temperature of the excision site, the operator of the liquid ejection device can control the strength of the liquid jet by calculating the cutting force based on the temperature of the excision site. Because it cools so that the excision site is in the optimum temperature range for excision, the operation of the liquid ejecting device becomes easy, and it is prevented from cutting to an unintended depth, so it is highly safe medical Equipment can be provided.

  Application Example 5 In the liquid ejecting apparatus, the gas ejecting opening includes the cooling unit.

  According to this, since the liquid ejected from the liquid ejecting opening is hardly affected by the cooling gas ejected from the gas ejecting opening, there is little possibility of displacement with respect to the excision site, and the excision ability can be maintained.

  Application Example 6 The liquid ejecting apparatus according to the above-described liquid ejecting apparatus, further including a suction pipe on an outer periphery of the gas ejecting pipe.

  Thereby, it can suppress that the excised tissue piece accompanying excision scatters outside.

  Application Example 7 In the liquid ejecting apparatus, a portion of the liquid ejecting tube that contacts the cooling gas is formed of a material having a thermal conductivity lower than 1 W / mK. .

  As a result, the portion of the liquid jet tube that contacts the cooling gas is difficult to cool, so the liquid is difficult to cool, and the viscosity of the liquid is not affected by the cooling gas. Since at least the tip of is formed of a material having biocompatibility, even if the liquid ejection opening touches the living body, it does not cause an allergic reaction of the living body, so that the safety of the living body is high.

  Application Example 8 In the liquid ejecting apparatus, the suction tube is formed of a material having a thermal conductivity lower than 1 W / mK.

  This reduces the cooling of the suction pipe with the cooling gas, so that the temperature of the cooling gas is not easily exchanged with the suction pipe, preventing the temperature of the cooling gas from rising. It is possible to prevent accidents caused by cooling when an unintended contact is made by a person who handles the device.

  Application Example 9 A medical device using the liquid ejecting apparatus.

  As a result, the resectable stress (cutting force) becomes substantially uniform, the depth of cutting can be easily controlled, and the affected tissue part is cooled, so that body fluid such as blood accompanying the cutting is generated. It is possible to provide a medical device that is extremely small and highly safe.

1 is a schematic diagram illustrating a liquid ejecting apparatus according to a first embodiment. FIG. 3 is a cross-sectional view illustrating an ejection site and an affected tissue site of the liquid ejection device according to the first embodiment. Sectional drawing explaining the excision process of the affected part tissue site | part by the liquid ejecting apparatus which concerns on 1st Embodiment. Sectional drawing explaining the area | region where the cooling gas by the liquid ejecting apparatus which concerns on 1st Embodiment hits a cutting location. Schematic which shows the liquid ejecting apparatus which concerns on 2nd Embodiment. FIG. 6 is a cross-sectional view illustrating a liquid ejecting apparatus according to a second embodiment. FIG. 9 is a cross-sectional view schematically illustrating a medical liquid ejecting apparatus according to a third embodiment.

  Hereinafter, the present embodiment will be described with reference to the drawings. Note that the drawings referred to in the following description are schematic views in which the vertical and horizontal scales of members or portions are different from actual ones for convenience of illustration.

(First embodiment)
FIG. 1 is a schematic diagram illustrating a liquid ejecting apparatus according to the present embodiment. In the present embodiment, a liquid ejecting apparatus as a medical water jet knife that cuts or incises a living tissue by ejecting liquid will be described. As shown in FIG. 1, the liquid ejecting apparatus 2 according to the present embodiment includes a liquid container 10 that stores liquids such as physiological saline and chemicals, a liquid supply pump 12 that sucks liquid from the liquid container 10, and a liquid supply A pulsating flow generation unit 14 that converts the liquid supplied from the pump 12 into a pulsating flow (hereinafter sometimes referred to as a pulse flow), a liquid jet pipe 16 that communicates with the pulsating flow generation unit 14, and the pulsating flow generation unit 14. The gas injection pipe 18 is provided in a protruding manner, the gas injection pump 20, and the drive circuit unit 22 that controls the operation of the liquid injection device 2. In the present embodiment, the liquid supply pump 12 that sucks up the liquid from the liquid container 10 is described. However, the liquid supply pump 12 is omitted when the liquid container 10 is supplied by a pressurized container or the natural flow of the liquid container 10. can do.

  The pulsating flow generation unit 14, the liquid supply pump 12, and the liquid container 10 are connected by a first connection tube 24A and a second connection tube 24B. Further, the gas injection pipe 18 and the gas injection pump 20 are connected by a gas transport tube 26.

  As the pulsating flow generation unit 14, any method that can convert a liquid into a pulsating flow and jet it in a pulsed manner such as a piezo method using a piezoelectric element or a bubble jet (registered trademark) method is applicable. Although it is possible, the pulsating flow generation unit 14 described below will be described by exemplifying a piezo method.

  The pulsating flow generation unit 14 includes a liquid chamber 30 whose volume can be changed, an inlet channel 30A and an outlet channel 30B communicating with the liquid chamber 30, and a volume that changes the volume of the liquid chamber 30 in response to the supply of a drive signal. A piezoelectric element 42 and a diaphragm 44 are provided as changing units.

  The liquid ejection pipe 16 has a liquid ejection flow path 32 communicating with a liquid chamber 30 formed inside the pulsating flow generation section 14, and a liquid ejection opening with a reduced flow path (not shown) at the tip. The part 28 is opened. The liquid ejection pipe 16 includes a liquid ejection opening portion 28 that communicates with an end portion different from the end portion that communicates with the liquid chamber 30 of the outlet channel. The liquid jet pipe 16 is inserted in the gas jet pipe 18. The liquid ejection pipe 16 is disposed so that the liquid ejection opening 28 and the gas ejection pipe 18 are concentric, but is not limited to being concentric.

  The gas injection pipe 18 is provided on the outer periphery of the liquid injection pipe 16 so as to have a double pipe structure. A gap formed between the inner peripheral surface of the gas injection pipe 18 and the outer peripheral surface of the liquid injection pipe 16 is a gas injection flow path 34, and gas is present at the end of the gas injection flow path 34 on the liquid injection opening 28 side. An injection opening 36 is provided.

  The cooling gas C ejected from the gas ejection opening 36 is ejected along the outer wall of the liquid ejection opening 28. The gas injection opening 36 spreads toward the tip so that the liquid injected from the liquid injection opening 28 and the conical cooling gas C injected from the gas injection opening 36 do not collide at the time of injection. It is formed in a shape. Thereby, since the liquid ejected from the liquid ejection opening 28 is not easily affected by the cooling gas C ejected from the gas ejection opening 36, there is little possibility of deviation from the excision point P (see FIG. 2). Ability can be maintained. It is desirable that the liquid ejection pipe 16 has a rigidity that does not deform or vibrate during the liquid ejection, and the gas ejection pipe 18 has a rigidity that does not deform or vibrate during the gas ejection.

  The operation of the liquid ejecting apparatus 2 ejecting the liquid or the operation of ejecting the cooling gas C is controlled by the drive circuit unit 22. The drive circuit unit 22 of the present embodiment is provided with a liquid ejection control unit 38 that controls the operation of ejecting liquid, and an ejection temperature control unit 40 that controls the temperature and operation of the cooling gas C to be ejected. The liquid injection control unit 38 is connected to the liquid supply pump 12 and the pulsating flow generation unit 14, and the injection temperature control unit 40 is connected to the gas injection pump 20 and the cooling unit 90. The liquid ejection control unit 38 controls the liquid supply pump 12 to change the amount of liquid supplied to the pulsating flow generation unit 14, and controls the pulsating flow generation unit 14 so that the pulsating flow generation unit 14 ejects the liquid. The conditions to do are changed. The liquid ejection control unit 38 supplies a drive signal for driving the piezoelectric element 42 so as to reduce the volume of the liquid chamber 30 to the piezoelectric element 42, and drives the piezoelectric element 42 so as to increase the volume of the liquid chamber 30 after the supply. The drive signal to be supplied is supplied to the piezoelectric element 42. The liquid ejection control unit 38 controls the start and stop of driving of the liquid supply pump 12. Further, the liquid ejection control unit 38 controls the pressure of the liquid that the liquid supply pump 12 supplies to the pulsating flow generation unit 14. The liquid ejection control unit 38 controls the ejection of liquid by the pulsating flow generation unit 14. Specifically, the liquid ejection control unit 38 controls the voltage applied to the piezoelectric element 42 of the pulsating flow generation unit 14.

  The injection temperature control unit 40 controls the cooling unit 90 to adjust the temperature of the cooling gas C injected by the gas injection pump 20 and increase / decrease or supply the supply amount of the cooling gas C cooled by the cooling unit 90. To stop.

  Further, the temperature of the cooling gas C controlled by the injection temperature control unit 40 may be a temperature at which the affected tissue site is frozen. If the affected tissue site is frozen, the affected tissue site becomes more inelastic, and the liquid ejection control can be less changed depending on the affected tissue site, so the burden on the user of the liquid ejecting apparatus 2 is reduced. To reduce.

  The cooling gas C cooled by the cooling unit 90 is harmless to the affected tissue site and the user of the liquid ejecting apparatus 2 by using, for example, nitrogen gas (nitrogen) and carbon dioxide gas (carbon dioxide). Further, by cooling the affected tissue part with the cooling gas C, the affected tissue part can be inactivated.

  The gas injection flow path 34 includes a cooling pipe part 92 that is piped to the pulsating flow generation part 14. Thereby, the pulsating flow generation unit 14 can be cooled by the cooling gas C cooled by the cooling unit 90. Further, by cooling the pulsating flow generation unit 14, the temperature rise of the ejected liquid can be suppressed.

  Next, the flow of the liquid in the liquid ejecting apparatus 2 configured as described above will be briefly described. The liquid stored in the liquid container 10 is sucked by the liquid supply pump 12, and is supplied to the pulsating flow generation unit 14 through the second connection tube 24B at a constant pressure. The pulsating flow generation unit 14 drives the piezoelectric element 42 to generate a pulsating flow in the liquid chamber 30, and ejects the liquid at high speed in a pulse form from the liquid ejection opening 28 through the liquid ejection channel 32.

  When the pulsating flow generation unit 14 stops driving, that is, when the volume of the liquid chamber 30 is not changed, the liquid supplied from the liquid supply pump 12 at a constant pressure passes through the liquid chamber 30 and is liquid. A continuous flow is ejected from the ejection opening 28.

  Here, the pulsating flow means a liquid flow in which the flow direction of the liquid is constant and the flow rate or flow velocity of the liquid is accompanied by a periodic or irregular fluctuation. The pulsating flow includes an intermittent flow in which the flow and stop of the liquid are repeated. However, since the flow rate or flow rate of the liquid only needs to fluctuate periodically or irregularly, it is not necessarily an intermittent flow.

  Similarly, ejecting the liquid in a pulse form means ejecting the liquid in which the flow rate or moving speed of the ejected liquid is changed periodically or irregularly. An example of pulsed injection is intermittent injection in which liquid injection and non-injection are repeated. However, since the flow rate or movement speed of the liquid to be injected only needs to fluctuate periodically or irregularly, it is not always intermittent injection. Need not be.

  Further, the liquid ejecting apparatus 2 may include a temperature measuring mechanism 8. The temperature measurement mechanism 8 is, for example, a non-contact type temperature measurement mechanism, and measures the temperature of the liquid ejection target. In the temperature measurement mechanism 8, a wiring (not shown) is connected to the drive circuit unit 22. In the temperature measurement mechanism 8, a wiring (not shown) is connected to the liquid ejection control unit 38.

  The temperature measurement mechanism 8 includes, for example, a non-contact type temperature measurement mechanism, so that the temperature measurement mechanism does not touch the liquid injection target or the liquid, so that the liquid injection is not an obstacle to the liquid injection. The injection target can be kept hygienic.

  FIG. 2 is a cross-sectional view showing an ejection site and an affected part tissue site of the liquid ejection device 2 according to the present embodiment. The injection part of the liquid injection device 2 is constituted by a double pipe, and the outer pipe is a gas injection pipe 18 and the inner pipe is a liquid injection pipe 16. A liquid ejection opening 28 is provided at the tip of the liquid ejection pipe 16. The liquid ejecting apparatus 2 performs excision of the excision site P by ejecting liquid from the liquid ejection opening 28 toward the excision site P. The liquid ejection opening 28 may have, for example, a shape that spreads in a trapezoidal shape toward the tip of the liquid ejection tube 16. As a result, the cooling gas C ejected from the gas ejection opening 36 flows along the outer wall of the liquid ejection opening 28, thereby affecting the ejection of the pulsed liquid ejected from the liquid ejection opening 28. In addition, the drainage fluid and the excised tissue pieces collected at the excision site P can be removed.

  The temperature measuring mechanism 8 receives the infrared rays D emitted from the excision site P and measures the surface temperature in a non-contact manner. The measurement result is sent to the drive circuit unit 22 and the liquid ejection control unit 38.

  The cutting force (cutting stress) at the excision site P correlates with a specific temperature at the excision site P, and the surface temperature of the excision site P in contact with the liquid is grasped, and it can be confirmed before the liquid jetting In addition, the strength of the liquid jet and the cooling temperature of the cooling unit 90 can be controlled according to the temperature of the excision site P.

  In addition, since the cutting force based on the temperature of the excision site P is calculated to control the strength of the liquid ejection, the operation of the liquid ejecting apparatus 2 is facilitated and the excision site P is cut to an unintended depth. Therefore, a highly safe medical device can be provided.

  Moreover, since the cooling temperature of the cooling unit 90 can also be controlled from the cutting ability of the liquid jet, the operation is merely to direct the liquid jetted to the excision site P, and the operation of the liquid jet device 2 becomes easy.

  FIG. 3 is a cross-sectional view illustrating the excision process of the affected tissue site by the liquid ejecting apparatus 2 according to the present embodiment. As already described, the cooling gas C ejected from the gas ejection opening 36 that flows along the outer wall of the liquid ejection opening 28 affects the ejection of the pulse flow ejected from the liquid ejection opening 28. Therefore, the pulse flow can be surely reached by the excision site P of the affected tissue site without being bent in flight. In addition, the drained fluid and the excised tissue pieces scattered around the excision site P can be removed.

  Furthermore, the cooling gas C that spreads and flows along the outer wall of the liquid ejection opening 28 to the conical side surface (C shape) cools the affected tissue site surface. By cooling the affected tissue site surface, the affected affected tissue site having flexibility can be substantially hardened, so that the energy of the pulse flow can be reduced from being absorbed and attenuated by the elasticity of the affected tissue site. Further, by cooling the surface of the affected tissue part, as shown in FIGS. 3A and 3B, the shear stress for excising and crushing the affected tissue part can be increased. By both the above actions, the excision ability can be synergistically improved.

Here, the area | region where the cooling gas C hits the cutting location P is demonstrated.
FIG. 4 is a cross-sectional view illustrating a region where the cooling gas C hits the excision site P by the liquid ejecting apparatus 2 according to the present embodiment. The liquid ejecting apparatus 2 may include a gas ejection adjusting unit 46 as a guide surface in the liquid ejecting opening 28. The gas injection adjusting unit 46 is configured to change the cooling gas C to be injected from the gas injection opening 36 according to the spread angle of the conical side surface of the outer wall of the liquid injection opening 28 according to the distance between the liquid injection opening 28 and the cut position P. Adjust the injection direction. Depending on the distance (D) between the liquid ejection opening 28 and the excision site P, the interval between the positions where the cooling gas C hits the excision site P becomes a predetermined value (L). The opening angle (θ) is adjusted.

  Here, an ultrasonic sensor or an infrared sensor may be used to measure the distance (D) between the liquid ejection opening 28 and the excision site P. In the case where the distance between the liquid ejection opening 28 and the excision site P is a relatively close distance D1, as shown in FIG. 4A, in order to set the interval L1 of the position where the cooling gas C hits the excision site P, The opening angle θ1 of the conical side surface of the outer wall of the liquid ejection opening 28 is set.

  On the other hand, when the distance (D) between the liquid ejection opening 28 and the excision point P is a distance D2 farther than the distance D1, it corresponds to the excision point P of the cooling gas C as shown in FIG. In order to make the position interval L2 equal to the interval L1, the opening angle θ2 of the conical side surface of the outer wall of the liquid ejection opening 28 is changed so as to satisfy the relationship θ2 <θ1.

  As a mechanism for changing the opening angle (θ) of the conical side surface of the outer wall of the liquid ejection opening 28, a spring material is used in advance, and the conical side surface of the outer wall of the liquid ejection opening portion 28 has a predetermined opening angle (θ). The amount of the cooling gas C is adjusted to adjust the opening angle (θ) of the conical side surface of the outer wall of the liquid ejection opening 28. That is, the larger the amount of the cooling gas C, the smaller the opening angle (θ) of the conical side surface of the outer wall of the liquid ejection opening 28 is. Therefore, by increasing the amount of the cooling gas C as the distance (D) between the liquid ejection opening 28 and the excision point P becomes longer (distance D2), the conical side surface of the outer wall of the liquid ejection opening 28 is increased. The opening angle (θ) becomes small (angle θ2).

  As a result, since the spread of the cooling gas C becomes small, the interval L2 at the position where the cooling gas C hits the excision site P can be matched with the interval L1. Furthermore, since the distance (D) between the liquid jet opening 28 and the excision point P is increased, the amount of the cooling gas C is increased even if the wind pressure of the cooling gas C is increased. A decrease in the wind pressure reaching the point P can be suppressed.

  Here, at least the tip of the liquid ejection opening 28 may be formed of a biocompatible material, and the tip of the liquid ejection opening 28 can be prevented from coming into contact with the living body and causing an allergic reaction. .

  In addition, the liquid jet tube 16 may be formed of a material having a porous structure or a thermal conductivity lower than 1 W / mK at least on the surface in contact with the cooled cooling gas C. By doing in this way, the liquid injection pipe 16 has a role of a heat insulating material, and it can reduce that the liquid injection pipe 16 and the gas injection pipe 18 are cooled with the cooled cooling gas C. Therefore, the temperature of the cooled cooling gas C is not easily exchanged with the liquid jet pipe 16 and the gas jet pipe 18, and the temperature of the cooled cooling gas C is prevented from rising. It is possible to prevent an accident caused by cooling when the operator of the injection device 2 makes an unintended contact.

  According to the present embodiment, the affected tissue part is cooled with the cooled cooling gas C, so that different strength differences can be made closer to each other, so that the resectable stress (cutting force) is almost equal. It becomes uniform and it becomes easy to control the cutting depth. In addition, since the affected tissue site is cooled, the generation of body fluid such as blood is reduced, and the affected tissue site can be easily seen. Further, the affected tissue part is cooled, so that the elasticity of the affected tissue part is weakened and the excision part can be cut deeply.

  Further, when the liquid jet tube 16 is used for surgery, if the affected tissue part is cooled with the cooled cooling gas C until it is frozen, bleeding of the affected tissue part accompanying cutting can be further reduced, and hemostasis work is performed. Since the operation time can be shortened, the safety of the living body is increased.

(Second Embodiment)
Next, a second embodiment will be described. In the description of this embodiment, the same components as those in the first embodiment are denoted by the same reference numerals, and the description thereof is omitted.
FIG. 5 is a schematic diagram illustrating the liquid ejecting apparatus according to the present embodiment. As shown in FIG. 5, the liquid ejecting apparatus 4 according to the present embodiment includes a suction pipe 48 protruding from the pulsating flow generation unit 14, a suction pump 50 as a suction unit, and sucked drainage and excised tissue. And a collection container 52 for accommodating the pieces. The suction pipe 48, the suction pump 50, and the collection container 52 are connected by a third connection tube 54.

  The suction pipe 48 is disposed on the outer periphery of the gas jet pipe 18 and is arranged so as to have a triple pipe structure including the liquid jet pipe 16. A gap formed between the inner peripheral surface of the suction pipe 48 and the outer peripheral surface of the gas injection pipe 18 is a suction flow path 56, and the suction opening 58 is provided at the end of the suction flow path 56 on the liquid injection opening 28 side. Is arranged. The gas injection pipe 18 is inserted in the suction pipe 48. And although the gas injection pipe 18 is arrange | positioned so that the gas injection opening part 36 and the suction pipe 48 may become concentric, it is not limited to concentricity.

  The suction pipe 48 and the gas injection pipe 18 may be formed of a material having a porous structure or a thermal conductivity lower than 1 W / mK at least on the surface in contact with the cooled cooling gas. An example of the material having a thermal conductivity lower than 1 W / mK is silicon. By doing in this way, it can reduce that the suction pipe 48 and the gas injection pipe 18 have a role of a heat insulating material, and the suction pipe 48 and the gas injection pipe 18 are cooled by the cooled cooling gas C. . Therefore, the temperature of the cooled cooling gas C is not easily exchanged with the suction pipe 48 and the gas injection pipe 18, and the temperature of the cooled cooling gas C is prevented from rising. It is possible to prevent an accident caused by cooling when the operator 4 makes an unintended contact.

  The operation in which the liquid ejecting apparatus 4 sucks the liquid is controlled by the drive circuit unit 22. As shown in FIG. 5, the drive circuit unit 22 of the present embodiment is provided with a suction control unit 60 that controls the operation of sucking the liquid, and the suction control unit 60 is connected to the suction pump 50. The suction control unit 60 controls the start and stop of the driving of the suction pump 50.

  Next, suction will be described. The liquid ejected from the liquid ejection opening 28 stays as drainage at the excision site P. In addition, a resected tissue piece is present in the affected area. The drainage and the excised tissue pieces are sucked from the suction opening 58 by the suction pump 50 and are stored in the recovery container 52 through the suction flow path 56 and the third connection tube 54. The suction pump 50 may be driven in conjunction with the driving of the pulsating flow generation unit 14, may be driven intermittently periodically, or may be driven when necessity arises.

  FIG. 6 is a cross-sectional view showing the liquid ejecting apparatus 4 according to this embodiment. The liquid ejecting apparatus 4 includes a triple pipe as an ejecting portion, a suction pipe 48 as an outer pipe, a gas jet pipe 18 as an inner pipe, and a liquid jet pipe 16 as an inner pipe. In addition, since the excised tissue piece can be collected by the suction tube 48, it is possible to suppress scattering to the outside.

  Further, by setting the ejection volume per unit time from the gas ejection pipe 18 to be larger than the suction volume per unit time, the excision site P is strongly sucked into the suction opening 58 and the excision site P is damaged. You can avoid that.

  Furthermore, even if the cooling gas C is not sent from the gas injection pipe 18 during the suction period, the excision site P can be prevented from being sucked by suction by communicating with the atmosphere.

  In the present embodiment, the cooling unit 90 provided between the gas injection pump 20 and the pulsating flow generation unit 14 in FIG. 1 is provided, the cooling unit 90 is provided in the gas injection opening 36, and a wiring (not shown) is provided in the drive circuit. It is connected to the unit 22.

  The cooling unit 90 is mesh-shaped and cools the gas by contacting with the gas. However, since the cooling unit 90 is provided in the gas injection opening 36, the liquid injection pipe 16 and the gas injection pipe 18 of the cooled cooling gas C are provided. Since there are few places to contact, heat efficiency is high and the power consumption accompanying cooling can be reduced.

  Further, by projecting the liquid jet pipe 16 forward from the gas jet pipe 18 disposed on the outer periphery thereof, the cooling gas C can be guided to the affected part along the liquid jet pipe 16 and the excision ability can be improved. .

  According to the present embodiment, it is possible to prevent the drained liquid or the excised tissue piece scattered by the liquid from scattering to the outside, and to suck the gas injection volume per unit time of the cooling gas C injected from the gas injection opening 36. By making it larger than the suction volume per unit time of the gas sucked by the opening 58, it is possible to prevent the suction opening 58 from adhering to the affected tissue site.

(Third embodiment)
Next, a third embodiment will be described. In the description of this embodiment, the same components as those in the first embodiment are denoted by the same reference numerals, and the description thereof is omitted.
FIG. 7 is a cross-sectional view schematically showing the medical liquid ejecting apparatus according to the present embodiment. As shown in FIG. 7A, the liquid ejecting apparatus 6 according to the present embodiment is used for clot crushing and has a space A having a space A filled with a liquid made of water or physiological saline. A catheter 82 as a body, a silica-based optical fiber 84 extending from the inside of the space A to the outside, and a holmium Yag laser (wavelength: 2.1 μm) (hereinafter simply referred to as “pulse laser”) as pulse light to the optical fiber 84 And a known laser oscillator 86 serving as a pulsating flow generator.

  The catheter 82 is formed in a tube shape from a known catheter material such as vinyl chloride or PCB (polychlorobiphenyl), and the distal end located on the left end side in the drawing is a liquid that opens the space A toward the outside. The injection opening 28 is formed.

  The tip end side (left end side in the figure) of the optical fiber 84 is a pulse laser irradiation portion 84A, and this irradiation portion 84A is located in the space A that is inside the liquid ejection opening 28. Therefore, when the pulse laser is irradiated, the liquid portion 88 in the vicinity of the irradiation portion 84A is expanded by the energy of the pulse laser, as schematically shown in FIG. The internal pressure of A rises, and the liquid becomes a liquid jet (jet) J by the increase of the internal pressure, and is ejected from the liquid ejection opening 28 to the outside. At this time, the liquid is supplied from the liquid supply pump 12 into the space A of the catheter 82 substantially continuously or in synchronization with the pulse laser irradiation, and the liquid is always filled in the space A immediately before the pulse laser irradiation. It is like that.

  According to the present embodiment, the liquid at a high temperature is ejected by the irradiation of the pulse laser from the laser oscillator 86. However, in order to cool the portion to be ejected, the portion to be ejected has the thermal effect of the ejected liquid. It is hard to receive. Therefore, for example, in the case of living body surgery, it is possible to prevent burns at locations to be ejected by the ejected liquid.

(Modification 1)
A gas container filled with a gas having a cooling effect may be communicated with the gas ejection pipe without having a cooling unit for cooling the gas in the liquid ejection device.

  According to this, since the liquid ejecting apparatus does not have a cooling unit, the power consumption of the liquid ejecting apparatus can be achieved.

  DESCRIPTION OF SYMBOLS 2, 4, 6 ... Liquid injection apparatus 8 ... Temperature measurement mechanism 10 ... Liquid container 12 ... Liquid supply pump 14 ... Pulse generation part 16 ... Liquid injection pipe 18 ... Gas injection pipe 20 ... Gas injection pump 22 ... Drive circuit unit 24A ... 1st connection tube 24B ... 2nd connection tube 26 ... Gas conveyance tube 28 ... Liquid injection opening 30 ... Liquid chamber 30A ... Inlet flow path 30B ... Outlet flow path 32 ... Liquid injection flow path 34 ... Gas injection flow path 36 ... Gas injection opening 38 ... Liquid injection control unit 40 ... Injection temperature control unit 42 ... Piezoelectric element (volume changing unit) 44 ... Diaphragm 46 ... Gas injection adjustment unit (guidance surface) 48 ... Suction pipe 50 ... Suction pump 52 ... Recovery container 54 ... 3rd connection tube 56 ... Suction flow path 58 ... Suction opening 60 ... Suction control part 82 ... Catheter 84 ... Optical fiber 84A ... Cum 86 ... laser oscillator (pulsating flow generation section) 88 ... partial 90 ... cooling unit 92 ... cooling pipe portion.

Claims (9)

A pulsating flow generator for imparting pulsating flow to the liquid ;
A liquid ejection pipe that communicates with the pulsating flow generation section and ejects liquid from the liquid ejection opening;
A cooling unit for cooling the gas;
Disposed on an outer periphery of the liquid injection pipe, comprising a gas injection opening, a gas injection pipe for injecting cooled cooling air by the cooling unit,
Have
The liquid ejecting apparatus according to claim 1, wherein the liquid ejecting pipe is formed with a guide surface for guiding an ejection direction of the cooling gas ejected from the gas ejecting pipe. The liquid ejecting apparatus according to claim 1,
A liquid having a gas injection adjusting unit for adjusting an injection direction of the cooling gas in accordance with a distance between the liquid injection opening and an injection target from which the liquid is injected from the liquid injection opening. Injection device. The liquid ejecting apparatus according to claim 1 or 2,
The outer diameter of the liquid jet tube is a shape that widens toward the tip,
The liquid ejecting apparatus according to claim 1, wherein the cooling gas is guided along an outer wall of the liquid ejecting opening. The liquid ejecting apparatus according to any one of claims 1 to 3,
A temperature measuring mechanism for measuring the temperature of a jetting target from which liquid is jetted from the liquid jetting opening,
A liquid ejecting apparatus further comprising: In the liquid ejecting apparatus according to any one of claims 1 to 4,
A liquid ejecting apparatus comprising the cooling unit in the gas ejection opening. In the liquid ejecting apparatus according to any one of claims 1 to 5,
The liquid ejecting apparatus further includes a suction tube on an outer periphery of the gas ejecting tube. The liquid ejecting apparatus according to any one of claims 1 to 6,
A portion of the liquid jet pipe that contacts the cooling gas is formed of a material having a thermal conductivity lower than 1 W / mK. The liquid ejecting apparatus according to claim 6 or 7,
The suction pipe is formed of a material having a thermal conductivity lower than 1 W / mK.   A medical device using the liquid ejecting apparatus according to claim 1.

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