# US 9,750,958 B2 · Dosimetric scintillating screen detector for charged particle radiotherapy quality assurance

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- Number: US 9,750,958 B2
- Document ID: US9750958B2
- Status: Granted
- Kind: B2
- Application number: 14/528,079
- Filed: 2014-10-30
- Published: 2015-03-12
- Granted: 2017-09-05
- Earliest claimed: 2012-02-23
- Applicants: Steven M. Ebstein
- Inventors: Steven M. Ebstein
- Web page: https://patentgrep.com/patent/US9750958B2

## CPC

- A61N 5/1075: {for testing, calibrating, or quality assurance of the radiation treatment apparatus}
- A61N 2005/1076: {using a dummy object placed in the radiation field, e.g. phantom}
- A61N: ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY (measurement of bioelectric currents A61B; surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body A61B18/00; anaesthetic apparatus in general A61M; incandescent lamps H01K; infrared radiators for heating H05B)

## Abstract

An apparatus and method are provided for performing Quality Assurance of complex beams of penetrating radiation inside a patient. A detector with a transverse scintillating screen images the radiation inside a tissue phantom with high spatial resolution. The scintillator is comprised of a mixture of two or more scintillators emitting different spectra of light and having different characteristic responses as a function of the beam LET value. The optics relaying the scintillation output have variable transmission with wavelength, further shaping the spectrum of light transmitted to the imaging sensor which also has spectrally varying sensitivity. Parameters of the scintillator construction, the optics, and the imaging sensor are chosen so the output of the composite detector is proportional to a characteristic of the input beam, for example the dose deposited as a function of depth inside the tissue phantom.

## Claims

### Claim 1

An apparatus for determining the spatial distribution and intensity of a penetrating radiation beam characterized generally by a propagation direction inside a body, the apparatus comprising:
a tissue phantom disposed between a radiation source and a radiation detector;
a scintillating screen disposed behind the tissue phantom for emitting light in response to the radiation received by the scintillating screen, the scintillating screen comprising a mixture of at least two scintillators wherein each scintillator has a different characteristic response and a different spectral output;
a means of optical communication between the output of the scintillating screen and at least one imaging sensor, wherein the means of optical communication has a nonuniform spectral transmission; and
at least one imaging sensor in optical communication with the scintillating screen for providing a high resolution imaging sensor output indicative of the spatial distribution and intensity of the radiation beam, wherein the imaging sensor has a nonuniform spectral sensitivity;
wherein the composition of the scintillating screen, the means of optical communication, and the at least one imaging sensor form a system wherein the relative contribution of the at least two scintillators of the mixture produce an imaging sensor output which is proportional to a characteristic of the radiation beam incident on the scintillating screen at each measurement position accessible with the tissue phantom;
wherein each scintillator of the mixture contributes a detection signal per deposited energy Dn(LET,F)=∫dλρnSn(λ)En(LET,F)An(λ)Q(λ)T(λ) to the total imaging sensor output and a fractional contribution
f
n
=
D
n
⁡
(
LET
,
F
)
∑
i
⁢
D
i
⁡
(
LET
,
F
)
to the total imaging sensor output;
wherein n is the index of the nth scintillator in the mixture, Dn(LET,F) is the detection signal per deposited energy for the nth scintillator as a function of the linear energy transfer (LET) and fluence (F), ρn is the areal density of the nth scintillator, Sn(λ) is the characteristic spectrum of the nth scintillator, En(LET,F) is the luminous efficiency of the nth scintillator as a function of the linear energy transfer (LET) and fluence (F), An(λ) is the attenuation factor for the nth scintillator due to self-absorption and scattering by the scintillation layer, Q(λ) is the spectral sensitivity of the imaging sensor, and T(λ) is the spectral transmission of the means of optical communication;
and wherein the fractional contribution, fn, of at least one scintillator of the mixture to the sensor output varies by at least 3% from what it would be with a means of optical communication having uniform spectral transmission T(λ)=1 and with the at least one imaging sensor having uniform spectral sensitivity Q(λ)=1 for a beam with LET and fluence that is clinically relevant.

### Claim 2 (depends on 1)

The apparatus as set forth in claim 1, wherein the characteristic of the radiation beam is the dose.

### Claim 3 (depends on 1)

The apparatus as set forth in claim 1, wherein the characteristic of the radiation beam is the response of an ion chamber.

### Claim 4 (depends on 1)

The apparatus as set forth in claim 1, wherein the characteristic of the radiation beam is the relative biological efficiency.

### Claim 5 (depends on 1)

The apparatus as set forth in claim 1, wherein the scintillating screen comprises a mixture of at least two inorganic scintillators.

### Claim 6 (depends on 1)

The apparatus as set forth in claim 1, wherein the at least two scintillators are chosen from the group consisting of P11, P20, P43, P46, and P47.

### Claim 7 (depends on 1)

The apparatus as set forth in claim 1, wherein the at least two scintillators comprise P11 and P43.

### Claim 8 (depends on 1)

The apparatus as set forth in claim 1, wherein the scintillating screen comprises a planar screen disposed perpendicular to the propagation direction of the radiation beam.

### Claim 9 (depends on 1)

The apparatus as set forth in claim 1, wherein the means of optical communication comprise a fold mirror and a compound lens.

### Claim 10 (depends on 1)

The apparatus as set forth in claim 1, wherein the at least one imaging sensor comprises a CCD.

### Claim 11 (depends on 1)

The apparatus as set forth in claim 1, wherein the tissue phantom comprises polymer sheets.

### Claim 12 (depends on 1)

The apparatus as set forth in claim 1 wherein the tissue phantom comprises water.

### Claim 13 (depends on 1)

The apparatus as set forth in claim 1 wherein the means of optical communication include at least one filter with nonuniform spectral transmission.

### Claim 14 (depends on 1)

The apparatus as set forth in claim 1 wherein the means of optical communication include at least one filter with variable nonuniform spectral transmission.

### Claim 15 (depends on 1)

The apparatus as set forth in claim 1 wherein the at least one imaging sensor forms a multi-color image.

### Claim 16 (depends on 1)

The apparatus as set forth in claim 1 wherein the means of optical communication includes a dichroic mirror which separates the light emitted by the scintillating screen into two significantly non-overlapping spectral bands and forms two spatially distinct images on the at least one imaging sensor, and further wherein the two spatially distinct images are linearly combined to produce the high resolution imaging sensor output.

### Claim 17 (depends on 1)

The apparatus as set forth in claim 1 wherein the characteristic of the radiation beam includes the fluence.

### Claim 18 (depends on 7)

The apparatus as set forth in claim 7 wherein P11 has areal density ρ1, P43 has areal density ρ2, and the total areal density, ρ1+ρ2, is in the range 40-400 mg/cm2,
and wherein the fractional density of P11,
ρ
1
ρ
1
+
ρ
2
,
is in the range 10-40% and the fractional density of P43,
ρ
2
ρ
1
+
ρ
2
,
is in the range 60-90%.

### Claim 19 (depends on 13)

The apparatus as set forth in claim 13 wherein the fractional contribution, fn, of at least one scintillator of the mixture varies by at least 3% from what it would be with a filter having uniform spectral transmission.