Patent Application
20090304552
This art relates to a discharge apparatus, for example. Such a discharge apparatus and an injection apparatus are discussed in, for example, Japanese Laid-open Patent Publications No. 04-289457, No. 2006-166756, No. 2002-286732, and No. 2004-337734.
For example, a microinjection capillary is discussed in Japanese Laid-open Patent Publications No. 2006-166756. A first liquid layer to be injected to cells is held at the tip of the capillary. A second liquid layer is held on the first liquid layer in the capillary. The first and second liquid layers define an interface therebetween. A laser light absorber is dispersed into the second liquid layer, for example. The laser absorber absorbs laser light and generates light. As a result, the second liquid layer thermally expands. An expansion pressure of the second liquid layer is converted to an injection pressure of the first liquid layer, with the result that the first liquid layer is injected from the tip of the capillary. In this way, a liquid is injected to cells, for example.
Such a capillary has a problem of the laser light absorber in the second liquid layer mixing with the first liquid layer through the interface therebetween. The laser light absorber mixed with the first liquid layer is injected to cells. In addition, the first and second liquid layers should be layered in the capillary. It takes a lot of time and effort to form such a laminate. As a result, microinjection costs high.
It is an object of the present invention to provide a discharge apparatus, by which improved controllability of liquid discharge is achieved.
According to an aspect of an embodiment, a discharge apparatus for discharging a liquid includes a discharge outlet for discharging the liquid; a first conduit extending toward the discharge outlet; a second conduit having one end connected to the first conduit for flowing a gas therethrough the second conduit extending generally in the direction toward the discharge outlet and generally approaching the first conduit toward the portion where the second conduit is connected to the first conduit; a chamber connected to the other end of the second conduit; and a heater installed to the chamber for heating a gas in the chamber so as to cause the heated gas to flow into the second conduit and to push out the liquid out of the discharge outlet.
Hereinafter, an embodiment will be described with reference to the accompanying drawings.
A dish 16 is provided on the level surface of the operation stage 15. A culture solution is poured into the dish 16. Cells as a target of agent injection are dispersed into the culture solution. A silicon chip 17 is secured into the dish 16. The silicon chip 17 has plural through-holes 18 that pass through the chip from the front side to the rear side. A path 19 formed in the dish 16 is connected to each through-hole 18. A vacuum pump 21 is connected to the path 19. The vacuum pump 21 generates a negative pressure. Along with the generation of a negative pressure, the air or liquid can be sucked out of the path 19. A pressure regulating valve 22 is connected to the vacuum pump 21. The pressure regulating valve 22 adjusts a negative pressure of the vacuum pump 21. A tank 23 is inserted between the path 19 and the vacuum pump 21. As described below, the tank 23 stores a culture solution flowing from the dish 16.
A pressure pump 31 is connected to the proximal end of the first conduit 28. The pressure pump 31 supplies a predetermined pressure to the first conduit 28 and the capillary conduit 25. A pressure generated with the pressure pump 31 is kept at a predetermined level. A regulator 32 is inserted between the first conduit 28 and the pressure pump 31. The pressure in the first conduit 28 and the capillary conduit 25 is adjusted with the aid of the regulator 32. A pressure sensor 33 is provided in the supporting unit 24. The pressure sensor 33 detects a pressure in the first conduit 28. The pressure sensor 33 may be, for example, an optical fiber pressure sensor. The optical fiber pressure sensor includes an optical fiber. A film is formed at the tip of the optical fiber. The film formed on the tip of the optical fiber deforms in accordance with a pressure in the first conduit 28. The deformation of the film causes light interference phenomenon. A target pressure is detected based on the interference phenomenon.
The supporting unit 24 incorporates a positive pressure generating mechanism 34. The positive pressure generating mechanism 34 includes four first chambers 35, for example. Each first chamber 35 is filled with at least one of a rare gas such as argon or helium and nitrogen. Each first chamber 35 includes a first heat generator 36. A converting element for converting light energy to heat energy is used as the first heat generator 36. A temperature sensor 37 is connected to at least one of the first heat generators 36. The temperature sensor 37 detects the temperature of the first heat generators 36. A first irradiation mechanism 38 is provided opposite to each first heat generator 36. The first irradiation mechanism 38 applies, for example, pulse laser light to the first heat generators 36. When applied with the pulse laser light, the first heat generators 36 generate heat. Any black body that easily absorbs heat can be used as the converting element.
Each first chamber 35 is connected to a second conduit 39 formed in the supporting unit 24. The second conduit 39 extends in a direction orthogonal to the first conduit 28 and merges with the first conduit 28 at the tip end, that is, the downstream end. The second conduit 39 reduces a distance from the first conduit 28 toward the infusion port 26 of the capillary 14 and then merges with the first conduit 28. The second conduit 39 is opened only at the tip end. The first chamber 35 and the second conduit 39 are connected together with a branch conduit 41. The branch conduit 41 reduces a distance from the second conduit 39 toward the tip end of the second conduit 39 and merges with the second conduit 39. The first chamber 35 is opened only at the branch conduit 41. The branch conduit 41 merges with the second conduit 39 at regular intervals from the proximal end, that is, the upstream end to the tip end.
Likewise, the supporting unit 24 incorporates a negative pressure generating mechanism 42. The negative pressure generating mechanism 42 includes four second chambers 43, for example. Each second chamber 43 is filled with at least one of a rare gas such as argon or helium and nitrogen. Each second chamber 43 includes a second heat generator 44. A converting element for converting light energy to heat energy is used as the second heat generator 44. A second irradiation mechanism 45 is provided opposite to each second heat generators 44. The second irradiation mechanism 45 applies, for example, pulse laser light to the second heat generators 44. When applied with the pulse laser light, the second heat generators 44 generate heat. Any black body that easily absorbs heat can be used as the converting element.
Each second chamber 43 is connected to a third conduit 46 formed in the supporting unit 24. The third conduit 46 extends in a direction orthogonal to the first conduit 28 and merges with the first conduit 28 at the tip end, that is, the downstream end. The third conduit 46 reduces a distance from the first conduit 28 toward a direction away from the infusion port 26 of the capillary 14 and then merges with the first conduit 28. The third conduit 46 may merge with the first conduit 28 in a position closer to the upstream side of the first conduit 28 than that of the second conduit 39. The second chamber 43 and the third conduit 46 are connected together with a branch conduit 47. The branch conduit 47 reduces a distance from the third conduit 46 toward the tip end of the third conduit 46 and merges with the third conduit 46. The second chamber 43 is opened only at the branch conduit 47. The branch conduit 47 merges with the third conduit 46 at regular intervals from the proximal end, that is, the upstream end to the tip end.
The CPU 52 outputs controls signal to control driving of the vacuum pump 21 or the pressure pump 31. Likewise, the first irradiation mechanism 38 or the second irradiation mechanism 45 turns on/off pulse laser light, that is, switchingly starts/stops application of the laser light based on control signals output from the CPU 52. On the other hand, pressure or temperature information is sent from the pressure sensor 33 or the temperature sensor 37 to the CPU 52. As described below, the PCU 52 controls driving of the first irradiation mechanism 38 and the second irradiation mechanism 45 based on the pressure or temperature information. In this way, the CPU feedback-controls the infusion unit 12.
Consider that medical agent is injected to a cell. The capillary 14 is attached to the injection port 27 of the supporting unit 24. As shown in
On the other hand, the dish 16 is placed on the level surface of the operation stage 15. A drop of suspension 62 is put into the dish 16. The suspension 62 includes a culture solution 63 and cells 64 dispersed into the culture solution 63. The CPU 52 drives the vacuum pump 21 with the dish 16 being placed on the operation stage 15. As the vacuum pump 21 is driven, a negative pressure is generated in the path 19. The pressure regulating valve 22 keeps the negative pressure in the path 19 at a predetermined level. Owing to the negative pressure generated in the path 19, the culture solution 63 is sucked out of the 16 toward the path 19 through the through-holes 18. The culture solution 63 flows into the tank 23. The culture solution 63 is stored in the tank 23 to prevent intrusion of the culture solution 63 into the pressure regulating valve 22 or the vacuum pump 21. In step S2, the cells 64 dispersed in the culture solution 63 are adsorbed at a predetermined position, that is, an opening of each through-hole 18 and trapped.
Along with forward movement of the infusion unit 12, the capillary 14 is inserted to the culture solution 63 in the dish 16. As shown in
The second conduit 39 reduces a distance from the first conduit 28 toward the infusion port 26 and then merges with the first conduit 28, so the airflow 71 is generated toward the injection port 27, that is, the infusion port 26 along an inner wall of the first conduit 28. The second conduit 39 extends toward the downstream end of the first conduit 28 with a certain angle to the first conduit 28. Thus, the airflow 71 generated in a direction from the second conduit 39 to the first conduit 28 is expressed by an inclination component 71a that crosses the axis of the first conduit 28 at a predetermined inclination angle. The inclination component 71a is expressed by an axial component 71b extending to the downstream end of the first conduit 28 in the axial direction of the first conduit 28 and an orthogonal component 71c extending in a direction orthogonal to the axis of the first conduit 28. The airflow 71 of the axial component 71b acts on the interface of the medical agent 61. A pressure acting on the medical agent 61 increases due to the airflow 71. The airflow 71 is turned into an injection pressure. As a result, very small amount of medical agent 61 is injected from the infusion port 26. The medical agent 61 is injected to the cell 64.
After the injection of the medical agent 61, the infusion unit 12 moves backward away from the culture solution 63. At this time, the pressure pump 31 applies a predetermined pressure to the first conduit 28 and the capillary conduit 25. After that, in step 5, the CPU 52 checks whether injection to all the cells 64 is completed. After the completion of injecting the agent to all the cells 64, the processing of the CPU 52 is terminated. On the other hand, if injection to any cell 64 is not completed, the CPU 52 repeats the processing from step S3.
At the time of setting the above pulse laser light irradiation conditions, the CPU 52 references the pressure information sent from the pressure sensor 33. At the same time, the CPU 52 references the temperature information sent from the temperature sensor 37. Based on the referenced information, the CPU 52 determines a relationship between a laser light irradiation time and its output value, temperature rise of the first heat generator 36, and a pressure of the first conduit 28. Such a relationship may be determined prior to the injection. The previously determined relationship may be stored in the memory 53. In this way, an injection amount of the medical agent 61 is determined based on how much a pressure of the first conduit 28 and a pressure of the capillary conduit 25 increase. Besides, the CPU 52 may reference pressure information and temperature information at the time of outputting control signals. Even if this causes an error due to any external factor such as a change in ambient temperature, a pressure increase can be precisely controlled through a so-called feedback control.
According to the thus-structured microinjection apparatus 11, heat generation of the first heat generator 36 is utilized for applying an injection pressure. The temperature of a gas in the first chamber 35 increases and the gas expands along with the heat generation of the first heat generator 36. In this way, a pressure in the first chamber 35 increases. As a result, the airflow 71 is generated in a direction from the first chamber 35 to the second conduit 39. The second conduit 39 reduces a distanced from the first conduit 28 toward the infusion port 26 and then merges with the first conduit 28, so the airflow 71 from the first chamber 35 moves toward the infusion port 26. Such generation of the airflow 71 increases a pressure applied to the interface of the medical agent 61. As a result, an injection pressure is applied to the first conduit 28 and the capillary conduit 25 to eject very small of medical agent 61 from the infusion port 26. In this way, the airflow 71 is utilized for the application of the injection pressure, with the result that intrusion of a foreign material to the medical agent 61 can be securely prevented.
The inventors of the present invention have calculated an injection amount of medical agent by simulation. The calculation is performed under the following conditions. That is, an output power of the first irradiation mechanism 38 is set to 1 [W]. A pulse laser light irradiation time is set to 10 [ms] (1 ms×10 pulses). Provided that an energy conversion efficiency of the first heat generator 36 is 100 [%], 10 [mj] of heat energy is applied to a gas in the first chamber 35. Nitrogen is used as the gas under such a condition that an isovolumetric specific heat rate Cv=0.736 [J/gK] and density=1.250 [g/l] (at 0° C. and 1 [atm]). A nitrogen gas having a volume of 1 [ml] has a weight of 1.250 [mg]. At this time, the temperature of nitrogen in the first chamber 35 is raised from 0 [° C.] to 10.9 [° C.] based on the above heat energy. At this time, a pressure is changed almost in proportion to change in absolute temperature, so the pressure of nitrogen in the first chamber 35 is increased from 1.00 [atm] to 1.04 [atm]. In this way, a rapid pressure increase of 0.04 [atm] (≅4 kPa) is attained. In this way, if the medical agent 61 is water, water is injected in several tens of femtoliter from the capillary 14. In this way, it was confirmed that very small injection amount could be set.
Upon adjusting an injection pressure, the negative pressure generating mechanism 42 may be driven. In this case, the negative pressure generating mechanism 42 may be driven together with the positive pressure generating mechanism 34. The CPU 52 outputs a control signal to the second irradiation mechanism 45 as well as the first irradiation mechanism 38. The second irradiation mechanism 45 applies pulse laser light to the second heat generator 44 under predetermined irradiation conditions. An output power of the pulse laser light is set lower than that of pulse laser light applied to the first heat generator 36. In this way, the second heat generator 44 generates heat. Along with the heat generation of the second heat generator 44, the temperature of a gas in the second chamber 43 increases. Along with the temperature rise, the gas expands. As a result, a pressure in the second chamber 43 increases. Similar to the first chamber 35, the second chamber 43 is opened only at the branch conduit 47, so as shown in
The third conduit 46 reduces a distance from the first conduit 28 toward a direction away from the infusion port 26 and then merges with the first conduit 28, so the airflow 72 is generated toward the upstream end of the first conduit 28 along an inner wall of the first conduit 28. The third conduit 46 extends toward the upstream end of the first conduit 28 with a certain angle to the first conduit 28, so the airflow 72 generated in a direction from the third conduit 46 to the first conduit 28 is expressed by an inclination component 72a that crosses the axis of the first conduit 28 at a predetermined inclination angle. The inclination component 72a is expressed by an axial component 72b extending to the downstream end of the first conduit 28 in the axial direction of the first conduit 28 and an orthogonal component 72c extending in a direction orthogonal to the axis of the first conduit 28. The airflow 72 of the axial component 72b moves in a direction opposite to the medical agent 61. The airflow 71 reduces a pressure generated with the positive pressure generating mechanism 34 and acting on the interface of the medical agent 61. In other words, a negative pressure generated with the negative pressure generating mechanism 42 is applied to the interface of the medical agent 61. An output power of that of pulse laser light applied to the second heat generator 44 is set smaller than that of pulse laser light applied to the first heat generator 36, so the negative pressure generated with the negative pressure generating mechanism 42 and acting on the interface of the medical agent 61 due to the airflow 72 and the positive pressure acting on the interface of the medical agent 61 due to the airflow 71 could cancel each other. As a result, a positive pressure corresponding to a difference between the positive pressure and the negative pressure acts on the interface of the medical agent 61, and the medical agent 61 is injected from the infusion port 26. In this way, an injection pressure acting on the interface of the medical agent 61 is reduced compared with the case of using the positive pressure generating mechanism 34 alone. As a result, a smaller amount of medical agent 61 is injected from the infusion port 26. An injection pressure can be finely adjusted by controlling the positive pressure and the negative pressure in this way.
On the other hand, the negative pressure generating mechanism 42 may be driven at the time of stopping the injection of the medical agent 61 to the cells 64. In this way, at the time of injecting the medical agent 61, the CPU 52 outputs a control signal to the second irradiation mechanism 45. The second irradiation mechanism 45 irradiates the second irradiation mechanism 45 with pulse laser light under predetermined irradiation conditions. An output power of the pulse laser light is set equal to that of the pulse laser light applied to the first heat generator 36. The second heat generator 44 generates heat. As in the above example, the airflow 72 is generated in a direction from the second chamber 43 to the third conduit 46. The airflow 72 moves toward the upstream end of the first conduit 28 along an inner wall of the first conduit 28. As a result, a negative pressure acts on the interface of the medical agent 61. An output power of the pulse laser light applied to the second heat generator 44 is set equal to that of the pulse laser light applied to the first heat generator 36, so the negative pressure acting on the interface of the medical agent 61 due to the airflow 72 is equal to the positive pressure acting on the interface of the medical agent 61 due to the airflow 71. The positive pressure and the negative pressure completely cancel each other. Thus, the injection pressure applied to the interface of the medical agent 61 is set to zero. As a result, the injection of the medical agent 61 is stopped. The injection of the medical agent 61 to the cells 64 can be stopped by adjusting the positive pressure and the negative pressure in this way.
Further, pulse laser light may be sequentially applied to the plural first heat generators 36 upon the adjustment of an injection pressure. If a single first heat generator 36 is continuously applied with pulse laser light, the generator is heated all this while. As a result, the first heat generator 36 takes much time to dissipate the heat. If the first heat generator 36 cannot dissipate the heat well, a large temperature difference of the first heat generator 36 cannot be obtained between before and after pulse laser light application. Thus, in order to precisely control an injection amount of the medical agent 61, the first heat generator 36 needs to dissipate the heat enough. However, since the first heat generator 36 takes much time to dissipate the heat, there is a possibility of lowering efficiency of injection of the medical agent 61 to the cells 64. According to the embodiment, such a problem can be solved.
First, pulse laser light is applied to the first first heat generator 36 upon injection of the medical agent 61 to the cell 64. After the completion of the injection, the second first heat generator 36 is irradiated with pulse laser light for injection of the medical agent 61 to the next cell 64. From then on, the third one, the fourth one, the first one, . . . , of the first heat generators 36 are irradiated with pulse laser light upon each injection. As a result, it is possible to prevent such a situation that the temperature of any one of the first heat generators 36 excessively increases. Each first heat generator 36 has enough time to dissipate heat. A temperature rise of a gas can be precisely controlled with the thus-controlled first heat generators 36. Thus, an injection amount of the medical agent 61 is precisely controlled. At the time of adjusting the injection pressure, pulse laser light may be successively applied to the plural second heat generators 44 to generate a negative pressure.
On the other hand, pulse laser light may be applied to the plural first heat generators 36 at the same time upon adjusting an injection pressure. For example, if pulse laser light is applied to the four first heat generators 36 at the same time, gases in the first chambers 35 expand at the same time. As a result, as compared with the case of applying pulse laser light to only one first heat generator 36, an airflow is generated at a high flow rate. Then, a higher pressure acts on the interface of the medical agent 61. In this way, a high injection pressure is applied to the first conduit 28 and the capillary conduit 25. As a result, an injection amount of the medical agent 61 can be increased. Moreover, even though a high power of pulse laser light is not applied to one first heat generator 36 for a long time, a high injection pressure can be obtained. As a result, it is possible to prevent such a situation that the temperature of any one of the first heat generators 36 excessively increases. Similar to the above example, at the time of adjusting the injection pressure, pulse laser light may be successively applied to the plural second heat generators 44 to generate a negative pressure.
As shown in
In the capillary 14a, if an injection pressure is applied to the first conduit 28 and the capillary conduit 25, as shown in
In addition, as the heat generator, a heater such as heating wire or another type of heat generator that combines a magnetic coil and metal may be used. As is well known, if a current flows through the heating wire, the current is converted to heat in accordance with a resistance of the heating wire. In this way, the heating wire generates heat. On the other hand, the combination of a magnetic coil and metal realizes electromagnetic-induction heating. As is well known, if a current flows through the magnetic coil, a magnetic line is generated from the magnetic coil. The generated magnetic line acts on metal. As a result, an eddy current is generated in the metal. The eddy current flowing through the metal is converted to heat in accordance with a resistance of the metal. In this way, the metal generates heat.
A discharge apparatus according to an embodiment includes: a discharge outlet for discharging the liquid; a first conduit extending toward the discharge outlet; a second conduit having one end connected to the first conduit for flowing a gas therethrough, the second conduit extending generally in the direction toward the discharge outlet and generally approaching the first conduit toward the portion where the second conduit is connected to the first conduit; a chamber connected to the other end of the second conduit; and a heater installed to the chamber for heating a gas in the chamber so as to cause the heated gas to flow into the second conduit and to push out the liquid out of the discharge outlet.
In the liquid injection apparatus, a plurality of chambers may be connected to the second conduit. In such a liquid injection apparatus, heat generators generate heat in order in the plurality of chambers. Along with heat generation, airflows are successively generated. In this way, an injection pressure is intermittently applied to a capillary, for example. For example, a liquid is successively injected to a plurality of objects of liquid injection. The plurality of heat generators are used as above, so it is possible to prevent an excessive temperature rise in one heat generator and secure enough time to dissipate heat of the heat generator. On the other hand, heat generators may generate heat in a plurality of chambers at the same time. In this case, the degree of temperature increase is higher than that of one heat generator. As a result, a large airflow is generated. A high injection pressure is applied to the capillary.
The discharge apparatus may further include a check valve provided in the first conduit and controls a back-flow of a liquid from the injection port to the first conduit. In the liquid injection apparatus, a negative pressure is generated in the first conduit as the heat generator is cooled after heat radiation. Owing to the provision of the check valve, the back-flow of a liquid to the first conduit from the injection port is prevented even if a negative pressure is generated in the first conduit. For example, the back-flow of the liquid to the capillary is prevented.
The discharge apparatus may further include: a third conduit having one end connected to the first conduit for flowing a gas therethrough, the third conduit extending generally in the direction toward the discharge outlet and generally approaching the first conduit toward the portion where the second conduit is connected to the first conduit;
another chamber connected to the other end of the third conduit; and a heater the another chamber so as to cause the heated gas to flow into the third conduit and to control to push out the liquid out of the discharge outlet.
In this case, a plurality of auxiliary chambers may be connected to the third conduit. As in the above case, heat generators generate heat in order in the plurality of auxiliary chambers. Along with heat generation, airflows are successively generated. In this way, a negative pressure is intermittently applied to the injection port, for example. Such a negative pressure can be used for controlling the injection pressure. The plurality of heat generators are used as above, so it is possible to prevent an excessive temperature rise in one heat generator and secure enough time to dissipate heat of the heat generator. On the other hand, heat generators may generate heat in a plurality of chambers at the same time. In this case, the degree of temperature increase is higher than that of one heat generator. As a result, a large airflow is generated. A high injection pressure is applied to the capillary.
The thus-structured discharge apparatus is incorporated in, for example, an injection apparatus. The injection apparatus includes: a capillary having one end for injecting the liquid; a first conduit extending toward the other end of the capillary; a second conduit having one end connected to the first conduit for flowing a gas therethrough, the second conduit extending generally in the direction toward the discharge outlet and generally approaching the first conduit toward the portion where the second conduit is connected to the first conduit; a chamber connected to the other end of the second conduit; and a heater installed to the chamber for heating a gas in the chamber so as to cause the heated gas to flow into the second conduit and to push out the liquid out of the capillary. According to the injection apparatus, the same advantages as above can be attained.
An injection method according to another embodiment includes: generating heat with a heat generator installed to a chamber containing a gas so as to cause expansion of the gas, the chamber being connected to a second conduit connected to a first conduit connected to a capillary having an end for discharging the liquid therefrom; and generating an airflow from the second conduit toward another end of the capillary along with the expansion of the gas so as to increase a pressure acting on the liquid to discharge the liquid from the end of the capillary. Another chamber may connect to the second conduit and a heat generator may installed in the another chamber.
Along with the generation of the airflow, heat generators generate heat in order in a plurality of chambers. Along with heat generation, airflows are successively generated. In this way, an injection pressure is intermittently applied to the tip end of a capillary, for example. For example, a liquid is successively injected to a plurality of objects of liquid injection. The plurality of heat generators are used as above, so it is possible to prevent an excessive temperature rise in one heat generator and secure enough time to dissipate heat of the heat generator. On the other hand, heat generators may generate heat in a plurality of chambers connected to the second conduit at the same time upon the generation of the airflow. In this case, the degree of temperature increase is higher than that of one heat generator. As a result, a large airflow is generated. A high injection pressure is applied to the capillary.
The injection method may further include: generating heat with a heat generator in an auxiliary chamber so as to cause expansion of a gas in the chamber, the auxiliary chamber being connected to a third conduit connected to the first conduit; and generating an airflow from the third conduit to the first conduit, the airflow being in a direction opposite to the end of the capillary along with the expansion of the gas so as to reduce a pressure acting on the liquid to control injection of the liquid from the end of the capillary.
As in the above case, upon the generation of the airflow, heat generators may generate heat in order in a plurality of auxiliary chambers connected to the third conduit. As in the above case, along with heat generation, airflows are successively generated. In this way, a negative pressure is intermittently applied to the injection port, for example. Such a negative pressure can be used for controlling the injection pressure. The plurality of heat generators are used as above, so it is possible to prevent an excessive temperature rise in one heat generator and secure enough time to dissipate heat of the heat generator. On the other hand, upon the generation of the airflow, heat generators may generate heat in a plurality of auxiliary chambers connected to the third conduit at the same time. In this case, the degree of temperature increase is higher than that of one heat generator. As a result, a large airflow is generated. A high injection pressure is applied to the capillary.
An injection apparatus according to another embodiment, for injecting an introduction material into a minute object includes: a capillary having an injection port for being inserted to the minute object so as to inject the introduction material into the minute object, the injection port being provided at an end of the capillary; a first conduit extending toward the other end of the capillary; a chamber connected to the first conduit; a light source for applying a light beam; a heat generator installed to the chamber for heating a gas in the chamber through the application with the light beam so as to cause the heated gas to flow into the first conduit and to push out the introduction material out of the capillary; and a control unit for performing on/off control of the light source.
An injection apparatus according to another embodiment, for injecting an introduction material into a minute object includes: a capillary having an injection port for being inserted to the minute object so as to inject the introduction material into the minute object, the injection port being provided at an end of the capillary; a conduit connected to the injection port; a positive pressure generating unit connected to the conduit, for generating a positive pressure to be applied from the conduit toward the injection port, the positive pressure generating unit having a first chamber of a gas, and a first heat generator for heating the first chamber; a negative pressure generating unit connected to the conduit, for generating a negative pressure to be applied from the conduit toward a direction away from the injection port, the negative pressure generating unit including a second chamber of a gas, and a second heat generator for heating the second chamber; and a control unit for controlling heat generation of the first heat generator and that of the second heat generator.
According to the embodiments, it is possible to provide a discharge apparatus, an injection apparatus and an injection method, which can inject very small amount of introduction material. In addition, any foreign material is prevented from mixing in the introduction material.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2007-187679 | Jul 2007 | JP | national |
