CN114531768A - High-power solid target for medical nuclide production - Google Patents
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Abstract
The invention discloses a high-power solid target for producing medical nuclide, wherein a target sheet is arranged on the upper surface of the solid target and is used for receiving a proton beam and generating nuclear reaction to generate nuclear elements; a row of comb-shaped water tanks are arranged below the target sheet and are used for enabling the beam to penetrate through the target sheet and then enter the water tanks to take away heat; a set included angle exists between the direction of the proton beam current and the target sheet; an energy deposition layer is arranged between the target and the water tank and used for selecting the energy of the beam current and sealing the water tank and the target; the invention relates to a method for preparing a solid target, which is characterized in that the width ratio of tooth grooves to teeth of the solid target is as follows: 1 is improved to be 2:1, increasing the area of beam current entering a water tank by one half; the traditional single-layer target sheet and the interlayer are transformed into the target sheet of the composite layer and the interlayer of the composite layer, so that the heat conducting performance of the area with a low nuclear reaction section is enhanced, the beam power borne by the solid target is improved from several kilowatts to 20kW, and the yield of the radioactive nuclide is improved.
Description
Technical Field
The invention belongs to the technical field of application of a high-current proton cyclotron, and particularly relates to a high-power solid target for producing medical nuclide by using a medium-energy proton beam.
Background
Short-lived radionuclides produced using an intermediate energy proton beam are useful in imaging (e.g., Sr-82, As-72), alpha-emitter nuclides (e.g., Ac-225), and in diagnostic and therapeutic applications (e.g., Cu-67). The radionuclide has wide prospects in the imaging of tumor specificity imaging, PET immune imaging, myocardial imaging and the like. Compared with the currently common beta radionuclide therapy, the alpha-ray generated by the alpha-radionuclide has high energy and short range, has extremely strong radiation biological effect, accurate treatment and easy radiation protection, and simultaneously, the DNA fracture caused by the alpha-ray can not be repaired, so that the tumor cells at the focus part and the cancer cells under the anoxic condition can be effectively killed, and the research of the alpha-targeted medicament is rapidly progressed in recent years. In addition, the nuclide produced by the solid target plays an increasingly extensive and important role in the aspects of tumor diagnosis and treatment integrated development, novel targeting, immunotherapy curative effect evaluation and the like.
The nuclide component produced by the solid target has the functions of receiving beam current to generate nuclear reaction, cooling the target plate, absorbing the energy of the garbage beam current and the like. The medical nuclide irradiation target station of the medium-high energy cyclotron requires high beam power of a solid target and can meet the requirements of various high-power beam energies.
The reason that the fixed target manufactured according to the existing structure is ultrahigh in temperature is that high-power beam energy is higher, and the reason that the beam energy is higher, the temperature is high, the water in the water tank is easy to vaporize, the temperature of the water tank in a vaporization area is further increased, and meanwhile, the pressure is increased, and the solid target is damaged under the combined action of the temperature and the pressure.
The difficulty of solving the ultrahigh temperature of the fixed target is as follows: the target piece is made of germanium or thorium (beams are shot on the germanium or the thorium to be reflected and are respectively used for generating isotopes As-72 and actinium-225), the thermal conductivity of the germanium or the thorium is very low, although an interlayer is arranged below the target piece, the interlayer is copper and has a good thermal conductivity effect, and the lower surface of the copper sheet is tightly attached to the cold water tank, the heat generated by the beams cannot be taken away through the copper or the water due to the very low thermal conductivity of the germanium or the thorium.
Disclosure of Invention
The invention provides a high-power solid target for medical nuclide production, aiming at solving the problems that the temperature of the solid target is ultrahigh, the water in a water tank is easy to vaporize due to the ultrahigh temperature, pressure is generated after vaporization, and the target is broken by expansion if the pressure exceeds the limit in the prior art.
The invention adopts the following technical scheme for solving the problems in the prior art.
A high-power solid target for medical nuclide production is characterized in that a target sheet is arranged on the upper surface of the solid target and used for receiving proton beams and generating nuclear reaction to generate nuclear elements; a row of comb-shaped water channels are arranged below the target plate and are used for enabling beam current to penetrate through the target plate and then enter the water channels to take away heat; a set included angle exists between the proton beam direction and the target sheet;
the method is characterized in that:
an energy deposition layer is arranged between the target and the water tank and is used for selecting the energy of the beam current and sealing between the water tank and the target; the energy deposition layer comprises an energy deposition layer of a single-material target sheet, the energy deposition layer of the single-material target sheet comprises an energy deposition layer for producing a high-power solid target of medical nuclide actinium-225; or the energy deposition layer comprises an energy deposition layer of a composite target wafer comprising an energy deposition layer of a high power solid target for producing arsenic-72 medical nuclides; selecting the energy of the passing beam correspondingly for each layer of the composite layer;
the sequence of the energy deposition layers of the high-power solid target for producing the medical nuclide actinium-225 from top to bottom is as follows: the first layer is thorium and is used for nuclear reaction between a proton beam current with the energy range of 100MeV-60MeV and thorium element; the second layer is copper and is used for energy deposition and heat conduction of beam current with energy ranging from 60MeV to 45 MeV; the third layer is water and copper, and is used for beam energy deposition and heat conduction with the energy range between 45MeV and 0 MeV.
The first layer has a thickness of 1.15 mm, 1.15 ═ 8.3 × sin θ, where 1.15 is the thickness, 8.3 is the throw, θ is 8 °; the thickness of the second layer is 0.3 mm, 0.3 ═ 2.14 × sin θ: the thickness of the third layer is 3.75 mm, 3.75 ═ 7 × sin θ.
The comb-shaped water tank is provided with tooth sockets for storing water and teeth for spacing the adjacent tooth sockets; the width of the tooth groove is larger than that of the tooth as much as possible; the width to height ratio of each gullet is about 1: 7; the width of each tooth is 0.4-4 mm; the width of each tooth slot is 0.8-2 mm, and the total number of the cooling water grooves is 20.
The proton beam direction and the target sheet have a set included angle, the included angle is reduced along with the increase of proton power in the design stage, after design and shaping, the angle is not changed, and when the beam energy is 20000 watts, the selected angle theta is 8 degrees.
The sequence of the energy deposition layers of the high-power solid target for producing the arsenic-72 medical nuclide from top to bottom is as follows: the first layer is copper and is used for energy deposition and heat conduction of beam current with energy ranging from 70MeV to 37 MeV; the second layer is germanium and is used for nuclear reaction of a proton beam current with energy ranging from 37MeV to 27MeV and germanium element; the third layer is copper; energy deposition and heat conduction for a beam of energy ranging between 27MeV and 18 MeV; the fourth layer is germanium and is used for nuclear reaction of a proton beam current with the energy range of 18MeV-5MeV and germanium element; the fifth layer is copper; for energy deposition and heat conduction of a beam in the energy range between 5MeV and 0MeV, the layer of copper is followed by a water bath.
The thickness of the first layer is 0.65 mm, range: 4.71 mm: the thickness of the second layer is 0.22 mm, range: 1.64 mm: the thickness of the third layer is 0.1 millimeter, the range is 0.7 mm: the thickness of the fourth layer is 0.14 mm, the range is 1 mm: the thickness of the fifth layer is 2mm, wherein 0.07mm is used for beam energy deposition.
Advantageous effects of the invention
1. The invention overcomes the traditional prejudice, modifies the structure of the target sheet and the structure of the interlayer, modifies the traditional single-layer target sheet and the interlayer into the target sheet of the composite layer and the interlayer of the composite layer, thereby enhancing the heat-conducting property of the area with low nuclear reaction section, and simultaneously, because the thickness of the interlayer (copper) is modified from 2-4 cm to 0.3-3 mm and is far less than the range of beam current in the copper, the beam current of the area with low nuclear reaction section can pass through the copper sheet to enter the water tank to rapidly take away the heat.
2. The invention improves the width ratio of tooth grooves and teeth of the solid target, and the width ratio is 1:1 is improved to be 2:1, the area of the beam current entering the water tank is increased by one half, so that the heat dissipation effect of the solid target is further enhanced.
3. By improving the structure, the beam power borne by the solid target is increased from a few kilowatts to 20kW, and the yield of the radioactive nuclide is increased.
Drawings
FIG. 1 is a schematic diagram of a target structure;
FIGS. 2-1232 Th (P, x)225Ac nuclear reaction cross-sectional views;
FIG. 2-2. NatGe (p, x)72As nuclear reaction cross-sectional view;
FIG. 3-1 is a first schematic diagram of an energy deposition layer;
FIG. 3-2 is a second schematic view of an energy deposition layer;
FIG. 4 is a schematic diagram of target slot dimensions;
in the figure, 1: target sheet; 2: an energy deposition layer; 3: a target holder; 4: gullet (water spot); 5: tooth
Detailed Description
Design principle of the invention
1. The reason that the temperature of the existing target body structure is ultrahigh: firstly, beam current directly strikes a target, the target is made of germanium or thorium, and heat of the target is not conducted out due to the low heat conduction coefficient of the germanium or the thorium; secondly, the thickness of the interlayer copper between the target plate and the water tank is 2-4 cm, the range of the beam current in the copper is 1.3 cm, and the beam current cannot penetrate through the interlayer after exceeding the thickness, so that the beam current cannot penetrate through the interlayer and enter the water tank because the interlayer intercepts the beam current in the prior art although the water tank is arranged below the interlayer.
2. The improvement of the invention is as follows: firstly, according to the size of the nuclear reaction cross section area, dividing the nuclear reaction into a high-yield area and a low-yield area, wherein the low-yield area is analyzed by the accelerator with the maximum of 100Mv as shown in figure 2-1, the low-yield area is from 60MeV to 0MeV, the low-yield area accounts for about 55 percent, the low-yield area is analyzed by the accelerator with the maximum of 100Mv as shown in figure 2-2, the low-yield area is from 70MeV to 37MeV, 27MeV to 18MeV, 5MeV to 0MeV, and the low-yield area accounts for about 67 percent; secondly, yield of the low-yield area is abandoned, and the low-yield area is used as a high heat dissipation area: the beam in the low-yield area is applied to copper instead of germanium or thorium, and the yield of the beam applied to the copper is zero, but the heat conductivity coefficient of the copper is far higher than that of the germanium or thorium, so that the heat dissipation of the low-yield area of 67% is facilitated. And thirdly, reducing the thickness of the copper sheet. The thickness of the copper in the low yield area is 0.1-3 mm, and the beam can penetrate through the copper into the water tank because the range of the beam in the copper is 13 mm. Fourthly, improvement of the water tank. The proportion of tooth sockets (water storage) and teeth (metal) of a water tank in the prior art target is about 1:1, the ratio of the tooth sockets (water storage) to the teeth (metal) is improved to be 2:1, as shown in figure 2-1, a high-volume area accounts for 45%, if the proportion of the tooth sockets (water storage) to the teeth (metal) is 1:1, 22.5% of beam flow enters water in the water tank, in addition, 22.5% of beam flow hits on the metal in the water tank, if the proportion of the tooth sockets (water storage) to the teeth (metal) is 2:1, the beam flow entering the water is increased by half, and the heat removal speed is also increased by 1.5 times. And fifthly, balancing yield and heat dissipation. The purpose of dividing the high and low yield regions is to increase the yield. The 0-yield area cannot be divided too much for simple heat dissipation, the 0-yield area is too large, the high-yield area is reduced, and the high-yield area is reduced. Therefore, the high yield region is divided into the low yield regions on the premise that the total yield is increased.
Based on the principle, the invention designs the high-power solid target for medical nuclide production.
A high-power solid target produced by medical nuclide is shown in figure 1, wherein a target sheet 1 is arranged on the upper surface of the solid target, and the target sheet 1 is used for receiving proton beam and generating nuclear reaction to generate nuclear elements; a row of comb-shaped water channels are arranged below the target plate and are used for enabling beam current to penetrate through the target plate and then enter the water channels to take away heat; a set included angle exists between the proton beam direction and the target sheet;
the method is characterized in that:
an energy deposition layer 2 is arranged between the target and the water tank, and the energy deposition layer 2 is used for selecting the energy of the beam passing through and sealing between the water tank and the target 1; the energy deposition layer 2 comprises an energy deposition layer of a single-material target sheet, the energy deposition layer of the single-material target sheet comprises an energy deposition layer of a high-power solid target for producing medical nuclide actinium-225; or the energy deposition layer comprises an energy deposition layer of a composite target wafer comprising an energy deposition layer of a high power solid target for producing arsenic-72 medical nuclides; selecting the energy of the passing beam correspondingly for each layer of the composite layer;
as shown in fig. 2-1 and 3-1, the energy deposition layers of the high-power solid target for producing medical nuclide actinium-225 are sequentially arranged from top to bottom: the first layer is thorium and is used for nuclear reaction between a proton beam current with the energy range of 100MeV-60MeV and thorium element; the second layer is copper and is used for energy deposition and heat conduction of beam current with energy ranging from 60MeV to 45 MeV; the third layer is water and copper, and is used for beam energy deposition and heat conduction with the energy range between 45MeV and 0 MeV.
The first layer has a thickness of 1.15 mm, 1.15 ═ 8.3 × sin θ, where 1.15 is the thickness, 8.3 is the throw, θ is 8 °; the thickness of the second layer is 0.3 mm, 0.3 ═ 2.14 × sin θ: the thickness of the third layer is 3.75 mm, 3.75 ═ 7 × sin θ.
As shown in fig. 1 and 4, the comb-shaped water tank is provided with tooth sockets 4 for storing water and teeth 5 for spacing adjacent tooth sockets; the width of the tooth socket 4 is larger than that of the tooth 5 as much as possible; the width to height ratio of each tooth slot 4 is about 1: 7; the width of each tooth 5 is 0.4-4 mm; the width of each tooth slot 4 is 0.8-2 mm, and the total number of the cooling water grooves is 20.
The proton beam direction and the target sheet have a set included angle, the included angle is reduced along with the increase of proton power in the design stage, after design and shaping, the angle is not changed, and when the beam energy is 20000 watts, the selected angle theta is 8 degrees.
As shown in fig. 2-2 and 3-2, the energy deposition layers of the high-power solid target for producing arsenic-72 medical nuclide have the following sequence from top to bottom: the first layer is copper and is used for energy deposition and heat conduction of beam current with energy ranging from 70MeV to 37 MeV; the second layer is germanium and is used for nuclear reaction of a proton beam current with energy ranging from 37MeV to 27MeV and germanium element; the third layer is copper; energy deposition and heat conduction for a beam of energy ranging between 27MeV and 18 MeV; the fourth layer is germanium and is used for nuclear reaction of a proton beam current with the energy range of 18MeV-5MeV and germanium element; the fifth layer is copper; for energy deposition and heat conduction of a beam in the energy range between 5MeV and 0MeV, the layer of copper is followed by a water bath.
The thickness of the first layer is 0.65 mm, range: 4.71 mm: the thickness of the second layer is 0.22 mm, range: 1.64 mm: the thickness of the third layer is 0.1 millimeter, the range is 0.7 mm: the thickness of the fourth layer is 0.14 mm, the range is 1 mm: the thickness of the fifth layer is 2mm, wherein 0.07mm is used for beam energy deposition.
Example one
Take the production of Ac-225 nuclide as an example
Determining target material and size
For a 100MeV strong flow proton cyclotron, a 70-100MeV intermediate energy proton beam can be generated at present according to nuclear reaction232Th(p,x)225Ac cross-sectional diagram, wherein 40-100MeV proton beam can generate Ac-225, the energy range can be selected to be 60-100 MeV for improving Ac-225 yield, and after the beam energy is reduced to 60MeV, nuclear reaction is carried out232Th(p,x)225The reaction cross section of Ac is reduced and the yield is reduced. Therefore, considering the cost of the target comprehensively, after the beam current is transmitted for a certain distance L in the Th material, the residual garbage energy of the beam current is deposited into the interlayer, the target holder and the cooling water.
Assuming that the cross-section of the proton beam is circular, there is an angle between the target and the direction of the proton beam that decreases as the power of the proton beam increases, with an angle θ of 8 ° being currently chosen.
Heat source equation q k1 k2 qmax/2/(pi σ)2)*exp(-r2/(2*σ2))；
k1 and k2 are sine values of equivalent inclination angles of the beam current and the target surface;
qmax is the total beam power;
pi is the circumference ratio;
r2＝(x*k1)2+(y*k2)2
sigma is the standard deviation of the Gaussian distribution beam;
energy transfer distance L of protons on the target, relationship between target thickness d and inclination angle θ: d ═ L × sin (θ)
FIG. 2-1232Th(P,x)225Ac nuclear reaction cross-section
Determining material and size of target holder and cooling channel
Proton energies below 60MeV enter the target holder and the cooling water. Taking copper as a target holder material and water as cooling liquid as an example, parameters such as the width and the height of a cooling water tank are changed, so that the energy ratio of the proton beam deposited in the water and the Cu can be changed, the proton beam energy finally deposited in the thorium is as much as possible, and the temperature of the target holder and the wall surface of the target piece cannot damage the solid target. The energy barrier performance of the current target body structure can reach 20kW, and the yield of medical radioactive nuclide is effectively improved. The ratio of the width to the height of the cooling water tank is about 1:7, the ratio of the width of the cooling water tank to the width of the target fin is about 2:1, and the total number of the cooling water grooves is about 20.
Solid target for producing multiple nuclides
Solid targets such as those shown in the schematic target structures can be used for multiple radionuclide production. For metal thorium, thorium material is uniformly plated on a copper interlayer by adopting an electroplating process, and a cooling flow channel is formed by the copper interlayer and a target holder to combine a solid target for producing Ac-225. The nuclear reaction for producing Sr-82 is85Rb(p,4n)82Sr, RbCl is commonly used as a nuclear reaction substance at the time, RbCl is a powdery material, the powdery RbCl is firstly pressed to form a sheet structure, then the RbCl sheet is welded into a stainless steel shell through welding, and then the stainless steel shell and a target support form a cooling flow channel, so that the assembly of the solid target is realized. The production of different isotopes can be realized by replacing the target sheet.
As the beam parameters are basically the same, the two target plates can use the same target holder, and the standardization of the target holder and the target plate structure is realized.
It should be emphasized that the above-described embodiments are merely illustrative of the present invention and are not limiting, since modifications and variations of the above-described embodiments, which are not inventive, may occur to those skilled in the art upon reading the specification, are possible within the scope of the appended claims.
Claims (7)
1. A high-power solid target for medical nuclide production is characterized in that a target sheet is arranged on the upper surface of the solid target and used for receiving proton beams and generating nuclear reaction to generate nuclear elements; a row of comb-shaped water channels are arranged below the target plate and are used for enabling beam current to penetrate through the target plate and then enter the water channels to take away heat; a set included angle exists between the proton beam direction and the target sheet;
the method is characterized in that:
an energy deposition layer is arranged between the target and the water tank and used for selecting the energy of the beam current and sealing the water tank and the target; the energy deposition layer comprises an energy deposition layer of a single-material target sheet, the energy deposition layer of the single-material target sheet comprises an energy deposition layer for producing a high-power solid target of medical nuclide actinium-225; or the energy deposition layer comprises an energy deposition layer of a composite target wafer comprising an energy deposition layer of a high power solid target for producing arsenic-72 medical nuclides; each layer of the composite layer is correspondingly selected to pass through the beam energy.
2. The high power solid target for production of medical nuclides as in claim 1, wherein: the sequence of the energy deposition layers of the high-power solid target for producing the medical nuclide actinium-225 from top to bottom is as follows: the first layer is thorium and is used for nuclear reaction between a proton beam current with the energy range of 100MeV-60MeV and thorium element; the second layer is copper and is used for energy deposition and heat conduction of beam current with energy ranging from 60MeV to 45 MeV; the third layer is water and copper, and is used for beam energy deposition and heat conduction with the energy range between 45MeV and 0 MeV.
3. The high power solid target for production of medical nuclides as in claim 1, wherein: the first layer has a thickness of 1.15 mm, 1.15 ═ 8.3 × sin θ, where 1.15 is the thickness, 8.3 is the throw, θ is 8 °; the thickness of the second layer is 0.3 mm, 0.3 ═ 2.14 × sin θ: the thickness of the third layer is 3.75 mm, 3.75 ═ 7 × sin θ.
4. The high power solid target for production of medical nuclides as in claim 1, wherein: the comb-shaped water tank is provided with tooth sockets for storing water and teeth for spacing the adjacent tooth sockets; the width of the tooth groove is larger than that of the tooth as much as possible; the width to height ratio of each gullet is about 1: 7; the width of each tooth is 0.4-4 mm; the width of each tooth slot is 0.8-2 mm, and the total number of the cooling water grooves is 20.
5. The high power solid target for production of medical nuclides as in claim 1, wherein: the proton beam direction and the target sheet have a set included angle, the included angle is reduced along with the increase of proton power in the design stage, after design and shaping, the angle is not changed, and when the beam energy is 20000 watts, the selected angle theta is 8 degrees.
6. The high power solid target for production of medical nuclides as in claim 1, wherein: the sequence of the energy deposition layers of the high-power solid target for producing the arsenic-72 medical nuclide from top to bottom is as follows: the first layer is copper and is used for energy deposition and heat conduction of beam current with energy ranging from 70MeV to 37 MeV; the second layer is germanium and is used for nuclear reaction of a proton beam current with energy ranging from 37MeV to 27MeV and germanium element; the third layer is copper; energy deposition and heat conduction for a beam of energy ranging between 27MeV and 18 MeV; the fourth layer is germanium and is used for nuclear reaction of a proton beam current with the energy range of 18MeV-5MeV and germanium element; the fifth layer is copper; for energy deposition and heat conduction of a beam in the energy range between 5MeV and 0MeV, the layer of copper is followed by a water bath.
7. The high power solid target for production of medical nuclides as in claim 6, wherein: the thickness of the first layer is 0.65 mm, range: 4.71 mm: the thickness of the second layer is 0.22 mm, range: 1.64 mm: the thickness of the third layer is 0.1 millimeter, the range is 0.7 mm: the thickness of the fourth layer is 0.14 mm, the range is 1 mm: the thickness of the fifth layer is 2mm, wherein 0.07mm is used for beam energy deposition.
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN116193701A (en) * | 2023-04-23 | 2023-05-30 | 中国科学院合肥物质科学研究院 | Solid target system for radionuclide preparation |
| CN116193701B (en) * | 2023-04-23 | 2023-06-30 | 中国科学院合肥物质科学研究院 | Solid target system for radionuclide preparation |
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| CN114531768B (en) | 2023-03-10 |
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