Imaging system with detector adjustable in position and orientation relative to handle

Abstract

An imaging system comprising: M radiation detectors (radiation detector (i), i = l,..., M), where M is a positive integer; a handle; and M independent connectors (independent connector (i), i = 1,..., M). For each possible value of i, a separate connection (i) physically connects the radiation detector (i) to the handle. The imaging system has the following properties: (A) during rotation of the handle from one orientation to any other orientation, the M independent connectors do not change their size or shape; and (B) a handle, the M individual connectors and the M radiation detectors remaining fixed relative to each other during rotation of the handle.

Description

Technical Field

[0001] This application relates to the field of radiation detector technology, and more particularly to an imaging system having a detector whose position and orientation are adjustable relative to a handle. Background Technology

[0002] A radiation detector is a device for measuring the properties of radiation. Examples of these properties may include the spatial distribution of the intensity, phase, and polarization of the radiation. The radiation measured by a radiation detector may be radiation that has already passed through an object. The radiation measured by a radiation detector may be electromagnetic radiation, such as infrared light, visible light, ultraviolet light, X-rays, or gamma rays. The radiation may also be other types, such as alpha rays and beta rays. An imaging system may include one or more radiation detectors. Utility Model Content

[0003] An imaging system is disclosed herein, comprising: M radiation detectors (radiation detectors (i), i = 1, ..., M), where M is a positive integer; a handle; and M independent connectors (independent connectors (i), i = 1, ..., M). For each value of i, the independent connector (i) physically connects the radiation detector (i) to the handle. The imaging system has the following properties: (A) during rotation of the handle from one orientation to any other orientation, none of the M independent connectors changes their size or shape; and (B) the handle, the M independent connectors, and the M radiation detectors remain fixed relative to each other during rotation of the handle. M may be equal to or greater than 1.

[0004] In one aspect, the properties of the imaging system remain unchanged after the shape of any of the M independent connectors is changed.

[0005] In one aspect, each of the M independent connectors is capable of being manually bent and retaining its shape after bending.

[0006] In one aspect, each of the M independent connectors is a gooseneck tube.

[0007] In one aspect, for each value of i, the independent connector (i) includes a hollow tube (i) and multiple conductive wires extending in the hollow tube (i) and electrically connecting the handle to the radiation detector (i).

[0008] In one aspect, the handle includes: a battery configured to supply power to the M radiation detectors; and a wireless charging circuit configured to charge the battery.

[0009] In one aspect, the handle includes a voltage source configured to supply voltage between two electrodes of each of the sensing elements of the M radiation detectors.

[0010] In one aspect, the handle is configured to process data from the M radiation detectors.

[0011] In one aspect, the handle includes an interface for transmitting data from the handle to an external computer.

[0012] In one aspect, each of the M radiation detectors is at most 1 cm thick, at most 5 cm wide, and at most 5 cm long.

[0013] In one aspect, each of the M radiation detectors is configured to detect X-rays.

[0014] In one aspect, the imaging system also includes a common connector that physically connects each of the M individual connectors to the handle.

[0015] In one aspect, the common connector is a gooseneck tube.

[0016] In one aspect, the common connector can be bent manually and retain its shape after bending.

[0017] In one aspect, the properties of the imaging system remain unchanged after the shape of the common connector is changed.

[0018] In one aspect, the common connector includes a common hollow tube and multiple conductive wires that extend within the common hollow tube and assist in electrically connecting the handle to the M radiation detectors.

[0019] In one aspect, the surface texture of the handle prevents slippage when a person grips the handle. Attached Figure Description

[0020] Figure 1 A radiation detector according to an embodiment is schematically shown.

[0021] Figure 2 A simplified cross-sectional view of a radiation detector according to an embodiment is shown schematically.

[0022] Figure 3 A detailed cross-sectional view of a radiation detector according to an embodiment is shown schematically.

[0023] Figure 4 A detailed cross-sectional view of a radiation detector according to an alternative embodiment is shown schematically.

[0024] Figure 5An imaging system according to an embodiment is illustrated schematically.

[0025] Figure 6 An imaging system according to an alternative embodiment is illustrated schematically. Detailed Implementation

[0026] Radiation detector

[0027] Figure 1 A radiation detector 100 is schematically shown as an example. The radiation detector 100 may include an array of pixels 150 (also referred to as sensing elements 150). This array may be a rectangular array (such as...). Figure 1 (as shown), cellular array, hexagonal array, or any other suitable array. Figure 1 The example array of 150 pixels has 4 rows and 7 columns; however, in general, an array of 150 pixels can have any number of rows and any number of columns.

[0028] Each pixel 150 can be configured to detect radiation incident on it from a radiation source (not shown) and can be configured to measure characteristics of the radiation (e.g., particle energy, wavelength, and frequency). The radiation can include radiant particles such as photons (X-rays, gamma rays, etc.) and subatomic particles (alpha particles, beta particles, etc.). Each pixel 150 can be configured to count the number of radiant particles incident on it and whose energy falls into multiple energy bins over a period of time. All pixels 150 can be configured to count the number of radiant particles incident on it and falling into multiple energy bins simultaneously over the same period of time. When the incident radiant particles have similar energies, pixel 150 can be configured simply to count the number of radiant particles incident on it over a period of time without measuring the energy of individual radiant particles.

[0029] Each pixel 150 may have its own analog-to-digital converter (ADC) configured to digitize an analog signal representing the energy of an incident radiating particle into a digital signal, or to digitize an analog signal representing the total energy of multiple incident radiating particles into a digital signal. Pixels 150 may be configured to operate in parallel. For example, while one pixel 150 is measuring an incident radiating particle, another pixel 150 may be waiting for the radiating particle to arrive. Pixels 150 do not necessarily need to be individually addressable.

[0030] The radiation detector 100 described herein can be used in applications such as X-ray telescopes, X-ray mammography, industrial X-ray defect detection, X-ray microscopy or microradiography, X-ray casting inspection, X-ray non-destructive testing, X-ray welding inspection, and X-ray digital subtraction angiography. Using this radiation detector 100 in place of photographic plates, photographic films, light-excited phosphor plates (PSP plates), X-ray image intensifiers, scintillators, or other semiconductor X-ray detectors may be suitable.

[0031] Figure 2 The illustration schematically shows an embodiment. Figure 1 A simplified cross-sectional view of the radiation detector 100 along line 2-2. Specifically, the radiation detector 100 may include a radiation absorbing layer 110 and an electronic circuitry layer 120 (which may include one or more ASICs or application-specific integrated circuits) for processing and analyzing the electrical signals generated in the radiation absorbing layer 110 by incident radiation. The radiation detector 100 may or may not include a scintillator (not shown). The radiation absorbing layer 110 may include a semiconductor material such as silicon, germanium, GaAs, CdTe, CdZnTe, or combinations thereof. The semiconductor material may have a high-quality attenuation coefficient for the radiation of interest.

[0032] Figure 3 The illustration is shown as an example. Figure 1 A detailed cross-sectional view of the radiation detector 100 along line 2-2. Specifically, the radiation absorption layer 110 may include one or more diodes (e.g., pin or pn) formed by one or more discrete regions 114 of a first doped region 111 and a second doped region 113. The second doped region 113 may be separated from the first doped region 111 by an optional intrinsic region 112. The discrete regions 114 may be separated from each other by either the first doped region 111 or the intrinsic region 112. The first doped region 111 and the second doped region 113 may have opposite types of doping (e.g., the first doped region 111 is p-type and the second doped region 113 is n-type, or the first doped region 111 is n-type and the second doped region 113 is p-type). Figure 3 In the example, each discrete region 114 of the second doped region 113 forms a diode with the first doped region 111 and an optional intrinsic region 112. That is, in Figure 3 In the example, the radiation-absorbing layer 110 has multiple diodes (more specifically, 7 diodes corresponding to...). Figure 1 The array has 7 pixels (150) per row; for simplicity... Figure 3 Only two pixels 150 are marked in the image. Multiple diodes can have electrodes 119A as a common electrode. The first doped region 111 can also have multiple discrete portions.

[0033] Electronic circuitry layer 120 may include electronic system 121 adapted to process or interpret signals generated by radiation incident on radiation-absorbing layer 110. Electronic system 121 may include analog circuitry such as filter networks, amplifiers, integrators, and comparators, or digital circuitry such as microprocessors and memories. Electronic system 121 may include one or more analog-to-digital converters. Electronic system 121 may include components shared by multiple pixels 150 or components dedicated to a single pixel 150. For example, electronic system 121 may include an amplifier dedicated to each pixel 150 and a microprocessor shared among all pixels 150. Electronic system 121 may be electrically connected to pixels 150 via interconnect channels 131. The space between interconnect channels may be filled with filler material 130, which may increase the mechanical stability of the connection between electronic circuitry layer 120 and radiation-absorbing layer 110. Other bonding techniques may connect electronic system 121 to pixels 150 without using interconnect channels 131.

[0034] When radiation from a radiation source (not shown) impacts the radiation-absorbing layer 110 of a diode, the radiation particles can be absorbed and generate one or more charge carriers (e.g., electrons, holes) through various mechanisms. The charge carriers can drift to the electrode of one of the diodes under an electric field. This electric field can be an external electric field. Electrical contacts 119B can include multiple discrete portions, each electrically contacting a discrete region 114. The term "electrical contact" is used interchangeably with the term "electrode." In one embodiment, charge carriers can drift in multiple directions such that the charge carriers generated by a single radiation particle are substantially not shared by two different discrete regions 114 (here, "substantially not shared" means that less than 2%, less than 0.5%, less than 0.1%, or less than 0.01% of these charge carriers flow to a discrete region of the plurality of discrete regions 114 that is different from the discrete region to which the remaining charge carriers flow). The charge carriers generated by radiating particles incident on the footprint of one of these discrete regions 114 are substantially not shared by the other discrete regions 114. A pixel 150 associated with a particular discrete region 114 can be a region surrounding that discrete region 114 in which substantially all (more than 98%, more than 99.5%, more than 99.9%, or more than 99.99%) of the charge carriers generated by radiating particles incident therein flow towards that discrete region 114. That is, less than 2%, less than 1%, less than 0.1%, or less than 0.01% of these charge carriers flow out of that pixel 150.

[0035] Figure 4 An illustration of an alternative embodiment is shown. Figure 1A detailed cross-sectional view of the radiation detector 100 along line 2-2. More specifically, the radiation absorbing layer 110 may include resistors made of semiconductor materials such as silicon, germanium, GaAs, CdTe, CdZnTe, or combinations thereof, but not diodes. The semiconductor material may have a high-quality attenuation coefficient for the radiation of interest. In one embodiment, Figure 4 The electronic circuit layer 120 is similar in structure and function to Figure 3 The electronic circuit layer 120.

[0036] When radiation impacts the radiation-absorbing layer 110, which includes resistors but not diodes, it can be absorbed and generate one or more charge carriers through various mechanisms. The radiating particles can generate 10 to 100,000 charge carriers. These charge carriers can drift to electrical contacts 119A and 119B under an electric field. This electric field can be an external electric field. Electrical contact 119B can include multiple discrete sections. In one embodiment, charge carriers can drift in multiple directions such that charge carriers generated by a single radiating particle are substantially not shared by two different discrete sections of electrical contact 119B (here, "substantially not shared" means that less than 2%, less than 0.5%, less than 0.1%, or less than 0.01% of these charge carriers flow to a discrete section different from the discrete section to which the remaining charge carriers flow). Charge carriers generated by radiating particles incident on the space occupied by one of these discrete sections of electrical contact 119B are substantially not shared by the other discrete section of electrical contact 119B. A pixel 150 associated with a discrete portion of the electrical contact 119B can be a region surrounding that discrete portion, in which substantially all (more than 98%, more than 99.5%, more than 99.9%, or more than 99.99%) of the charge carriers generated by incident radiant particles flow to that discrete portion of the electrical contact 119B. That is, less than 2%, less than 0.5%, less than 0.1%, or less than 0.01% of these charge carriers flow out of the pixel associated with that discrete portion of the electrical contact 119B.

[0037] Imaging system

[0038] Figure 5 An imaging system 500 according to an embodiment is schematically illustrated. The imaging system 500 may include a handle 530 and one or more radiation detectors (e.g., radiation detectors 100.1 and 100.2), each of which is structurally and functionally compatible with... Figures 1 to 4 The imaging system 500 is similar to the radiation detector 100. In one embodiment, the imaging system 500 may further include two separate connectors 540.1 and 540.2 (as shown) that physically connect the handle 530 to the two radiation detectors 100.1 and 100.2, respectively.

[0039] Imaging systems maintain their size and shape

[0040] In one embodiment, the imaging system 500 may have the following properties: (A) during the rotation of the handle 530 from one orientation to any other orientation, the individual connectors 540.1 and 540.2 do not change their size or shape; and (B) the handle 530, the individual connectors 540.1 and 540.2, and the radiation detectors 100.1 and 100.2 remain fixed relative to each other during the aforementioned rotation of the handle 530. Therefore, an operator can hold the handle 530 with one hand and move (i.e., rotate and / or translate) the imaging system 500 by moving the handle 530 without changing the size or shape of the imaging system 500. The individual connectors 540.1 and 540.2, having sufficient rigidity, will ensure that the imaging system 500 possesses this property. However, this property does not require that the shape or size of the individual connectors 540.1 and 540.2 be non-adjustable.

[0041] The imaging system retains its size and shape after the individual connectors are bent and twisted.

[0042] In one embodiment, the aforementioned properties of the imaging system 500 remain unchanged after the shape of either of the independent connectors 540.1 and 540.2 is changed. In other words, after either of the independent connectors 540 is bent or twisted, or both bent and twisted simultaneously, the operator can hold the handle 530 with one hand and move (i.e., rotate and / or translate) the imaging system 500 by moving the handle 530 without changing the size or shape of the imaging system 500.

[0043] In one embodiment, the shape of either of the independent connectors 540.1 and 540.2 may be adjustable.

[0044] Independent connectors

[0045] In one embodiment, refer to Figure 5 Each of the independent connectors 540.1 and 540.2 can be manually bent and can retain its shape after bending. Therefore, the position and orientation of each of the radiation detectors 100.1 and 100.2 relative to the handle 530 can be adjusted and remain unchanged after said adjustment.

[0046] In one embodiment, each of the independent connectors 540.1 and 540.2 may be a gooseneck tube.

[0047] In one embodiment, each individual connector 540 may include a hollow tube (not shown) and multiple conductive wires (not shown) extending within the hollow tube and electrically connecting the handle 530 to the corresponding radiation detector 100. For example, individual connector 540.1 may include a first hollow tube and multiple conductive wires extending within the first hollow tube and electrically connecting the handle 530 to the corresponding radiation detector 100.1. As another example, individual connector 540.2 may include a second hollow tube and multiple conductive wires extending within the second hollow tube and electrically connecting the handle 530 to the corresponding radiation detector 100.2.

[0048] handle

[0049] In one embodiment, refer to Figure 5 The handle 530 may include a battery (not shown) configured to supply power to the radiation detectors 100.1 and 100.2. In one embodiment, the handle 530 may include a wireless charging circuit (not shown) configured to charge the battery.

[0050] In one embodiment, the handle 530 may include a voltage source (not shown) configured to supply voltage between two electrodes (119A and 119B) of each of the sensing elements 150 of all radiation detectors 100.1 and 100.2.

[0051] In one embodiment, the handle 530 may be configured to process data (e.g., image data) from radiation detectors 100.1 and 100.2.

[0052] In one embodiment, the handle 530 may include an interface 532 for transmitting data from the handle 530 to an external computer 550. The computer 550 may process data (e.g., image data) from radiation detectors 100.1 and 100.2.

[0053] In one embodiment, each of the radiation detectors 100.1 and 100.2 may be at most 1 cm thick, at most 5 cm wide, and at most 5 cm long.

[0054] In one embodiment, each of radiation detectors 100.1 and 100.2 can detect X-rays. Therefore, imaging system 500 can be used to capture X-ray images of human and animal teeth.

[0055] In one embodiment, the surface texture of the handle 530 prevents slippage when a person grips the handle 530.

[0056] In one embodiment, radiation detectors 100.1 and 100.2 of the imaging system 500 may be placed inside the patient's oral cavity (not shown) to capture two images of two teeth 560, respectively. In one embodiment, a radiation source 590 outside the patient's oral cavity may provide an X-ray beam 592 for capturing two images of the two teeth 560. In one embodiment, radiation detectors 100.1 and 100.2 may simultaneously capture two images of the two teeth 560, respectively.

[0057] Reference Figure 5 Although radiation source 590 is shown as a point, radiation source 590 can have any size and shape (i.e., radiation source 590 is not necessarily a point source).

[0058] The term "image" in this patent application (including the claims) is not limited to the spatial distribution of radiation properties (e.g., intensity). For example, the term "image" may also include the spatial distribution of the density of a substance or element.

[0059] Common connector

[0060] In one embodiment, refer to Figure 5 Independent connectors 540.1 and 540.2 can be directly and physically connected to the handle 530 (as shown in the figure). Specifically, the right ends of independent connectors 540.1 and 540.2 both contact the handle 530 (as shown in the figure). In one embodiment, the right ends of independent connectors 540.1 and 540.2 may contact the handle 530 at two different points (as shown in the figure); however, alternatively, the right ends of independent connectors 540.1 and 540.2 may contact the handle 530 at the same point (not shown).

[0061] In an alternative embodiment, refer to Figure 6 The common connector 610 can physically connect each of the individual connectors 540.1 and 540.2 to the handle 530 (as shown). Therefore, the individual connectors 540.1 and 540.2 physically connect the common connector 610 to the radiation detectors 100.1 and 100.2, respectively (as shown).

[0062] It should be noted that regardless of whether there is a common connector 610 in the imaging system 500 (such as... Figure 5 (As shown) or there is a common connector 610 (such as Figure 6 As shown in the diagram, the independent connectors 540.1 and 540.2 can be considered to physically connect the radiation detectors 100.1 and 100.2 to the handle 530, respectively.

[0063] In one embodiment, refer to Figure 6The common connector 610 may be a gooseneck tube. In one embodiment, the common connector 610 can be bent manually and retains its shape after bending.

[0064] In one embodiment, refer to Figure 6 After the shape of the common connector 610 is changed, the aforementioned properties of the imaging system 500 (now including the common connector 610) remain unchanged. In other words, after the shape of the common connector 610 is changed, the imaging system 500 still possesses the following properties: (A) during the rotation of the handle 530 from one orientation to any other orientation, the individual connectors 540.1 and 540.2 do not change their size or shape, and (B) the handle 530, the individual connectors 540.1 and 540.2, and the radiation detectors 100.1 and 100.2 remain fixed relative to each other during the aforementioned rotation of the handle 530. Therefore, the operator can hold the handle 530 with one hand and move it around (i.e., rotate and / or translate) by moving the handle 530. Figure 6 The imaging system 500, without changing Figure 6 The size or shape of the imaging system is 500.

[0065] In one embodiment, refer to Figure 6 The common connector 610 may include a common hollow tube (not shown) and multiple conductive wires (not shown) extending in the common hollow tube and assisting in electrically connecting the handle 530 to the radiation detectors 100.1 and 100.2.

[0066] Although various aspects and embodiments have been disclosed herein, other aspects and embodiments will be apparent to those skilled in the art. The various aspects and embodiments disclosed herein are for illustrative purposes only and are not intended to be limiting; the true scope and spirit are indicated by the appended claims.

Claims

1. An imaging system, characterized in that, include: There are M radiation detectors (radiation detector(i), i = 1, ..., M), where M is a positive integer; Handle; and M independent connectors (independent connector (i), i = l, ..., M); For each value of i, the independent connector (i) physically connects the radiation detector (i) to the handle; and The imaging system has the following properties: (A) during the rotation of the handle from one orientation to any other orientation, none of the M independent connectors change their size or shape; and (B) the handle, the M independent connectors, and the M radiation detectors remain fixed relative to each other during the rotation of the handle.

2. The imaging system according to claim 1, characterized in that, M＝1。 3. The imaging system according to claim 1, characterized in that, M>l。 4. The imaging system according to claim 1, characterized in that, The properties of the imaging system remain unchanged after the shape of any of the M independent connectors is changed.

5. The imaging system according to claim 1, characterized in that, Each of the M independent connectors can be bent manually and retains its shape after bending.

6. The imaging system according to claim 1, wherein, Each of the M connectors is a gooseneck tube.

7. The imaging system according to claim 1, characterized in that, For each value of i, the independent connector (i) includes a hollow tube (i) and multiple conductive wires extending in the hollow tube (i) and electrically connecting the handle to the radiation detector (i).

8. The imaging system according to claim 1, characterized in that, The handle includes: A battery is configured to supply power to the M radiation detectors; and A wireless charging circuit is configured to charge the battery.

9. The imaging system according to claim 1, characterized in that, The handle includes a voltage source configured to supply voltage between two electrodes of each of the sensing elements of the M radiation detectors.

10. The imaging system according to claim 1, characterized in that, The handle is configured to process data from the M radiation detectors.

11. The imaging system according to claim 1, characterized in that, The handle includes an interface for transmitting data from the handle to an external computer.

12. The imaging system according to claim 1, characterized in that, Each of the M radiation detectors is at most 1 cm thick, at most 5 cm wide, and at most 5 cm long.

13. The imaging system according to claim 1, characterized in that, Each of the M radiation detectors is configured to detect X-rays.

14. The imaging system according to claim 1, characterized in that, It also includes a common connector that physically connects each of the M individual connectors to the handle.

15. The imaging system according to claim 14, characterized in that, The common connector is a gooseneck tube.

16. The imaging system according to claim 14, characterized in that, The common connector can be bent manually and retains its shape after bending.

17. The imaging system according to claim 14, characterized in that, The properties of the imaging system remain unchanged after the shape of the common connector is changed.

18. The imaging system according to claim 14, characterized in that, The common connector includes a common hollow tube and multiple conductive wires that extend within the common hollow tube and assist in electrically connecting the handle to the M radiation detectors.

19. The imaging system according to claim 1, characterized in that, The surface texture of the handle prevents it from slipping when held by a person.

Images